Multiplex q-pcr arrays

ABSTRACT

This present disclosure provides methods and systems for measuring the concentration of multiple nucleic acid sequences in a sample. The nucleic acid sequences in the sample are simultaneously amplified, for example, using polymerase chain reaction (PCR) in the presence of an array of nucleic acid probes. The amount of amplicon corresponding to the multiple nucleic acid sequences can be measured in real-time during or after each cycle using a real-time microarray. The measured amount of amplicon produced can be used to determine the original amount of the nucleic acid sequences in the sample. Also provided herein are biosensor arrays, systems and methods for affinity based assays that are able to simultaneously obtain high quality measurements of the binding characteristics of multiple analytes, and that are able to determine the amounts of those analytes in solution. The present disclosure also provides a fully integrated bioarray for detecting real-time characteristics of affinity based assays.

CROSS-REFERENCE

This application is a continuation-in-part of U.S. patent application Ser. No. 15/689,461, filed Aug. 29, 2017, which is a continuation-in-part of U.S. patent application Ser. No. 13/854,857, filed Apr. 1, 2013, now U.S. Pat. No. 10,106,839, which is a divisional of U.S. patent application Ser. No. 11/844,996, filed Aug. 24, 2007, now U.S. Pat. No. 8,637,436, which claims the benefit of U.S. Provisional Patent Application Ser. No. 60/840,060, filed Aug. 24, 2006, each of which is incorporated herein by reference in its entirety.

BACKGROUND OF THE INVENTION

Nucleic acid target amplification assays such as polymerase chain reaction process (PCR), in principle, amplify and replicate specific sequences of nucleic acids of a DNA template in vitro. These assays have become a powerful tool in molecular biology and genomics, since they can increase the number of copies of target molecules with great specificity. It is of great interest to efficiently multiplex the amplification process and thus allow for multiple target amplification and quantification.

Biosensor detection systems take advantage of the selective interaction and binding (affinity) of certain biological molecules to identify molecular structures and furthermore measure levels of different analytes such as toxins, polymers, hormones, DNA strands, proteins, and bacteria. Affinity-based biosensors exploit selective binding and interaction of certain bio-molecules (recognition probes) to detect specific target analytes in biological samples. The performance of biosensors in terms of signal to noise ratio and dynamic range is generally constrained by the characteristics of the molecular recognition layer which captures the target analytes, and not by the transducer and read-circuitry. An advantage of biosensors is their capability to be implemented in parallel and in an array format. Biosensors in parallel may compensate for limited detection performance. Presently, densely packed biosensor arrays which detect thousands of different analytes simultaneously (microarrays) may be popular in Genomics, Proteomics, molecular diagnostics, and systems biology.

In conventional fluorescent-based microarrays and other extrinsic reporter-based (label-based) biosensors assays, the detection of captured analytes is usually carried out after the incubation step. In some cases, proper fluorescent and reporter intensity measurements are compromised in the presence of a large concentration of floating (unbound) labeled species in the incubation solution, whose signal can overwhelm the target-specific signal from the captured targets. When the incubation is ceased and the solution is removed from the surface of the array, the washing artifacts often occur that make the analysis of the data even more challenging. Thus there exists a need for affinity based sensors that are able to simultaneously obtain high quality measurements of the binding characteristics of multiple analytes, and that are able to determine the amounts of those analytes in solution.

The emerging high-through screening and point-of-care (PoC) diagnostics applications may demand the integration of the biochemical part (assays) of the detection platform with the transducer and the detection circuitry. A microarray is desired in the art that offers compact and cost-efficient solutions with a high production yield and robust functionality.

Affinity-based biosensors exploit selective binding and interaction of certain bio-molecules (recognition probes) to detect specific target analytes in biological samples. The essential role of the biosensor platforms and the parallel and miniaturized version of them as microarrays are to exploit specific bindings of the probe-target complexes to produce detectable signals, which correlate with the presence of the targets and conceivably their abundance. The essential components of such a system include the molecular recognition layer (capturing probes) integrated within or intimately associated with a signal-generating physiochemical transducer and a readout device.

To generate target-specific signal, the target analytes in the sample volume generally first need to collide with the recognition layer, interact with the probes, bind to the correct probes, and ultimately take part in a transduction process. The analyte motion in typical biosensor settings (e.g., aqueous biological buffers) can be dominated by diffusion spreading, which from a microscopic point of view is a probabilistic mass-transfer process (modeled as a random walk for each analyte molecule). Accordingly, analyte collisions with probes become a stochastic process. Moreover, because of the quantum-mechanical nature of chemical bond forming, the interaction between the probes and the analytes molecules is also probabilistic, thus further contributing to uncertainty and noise corruption of the measured data in biosensors and microarrays. We view such phenomena as inherent noise in the detection system, which results in unavoidable uncertainties even when the measurements are noiseless. Such inherent noise is essentially inevitable since it originates from the stochastic nature of molecular-level interactions. Its examples include Poisson noise sources in microarrays and image sensor detection shot-noise.

Beside the inherent noise, other non-idealities also corrupt the signal obtained by the microarray experiments. Examples of such phenomena include probe density variations, sample preparation systematic errors, and probe saturation. We define systematic errors as the unwanted deviations from the intended detection procedure. If these errors are accurately evaluated, in theory, they can be compensated by post experiment data processing.

Gene expression microarrays are a widely used microarray platform. These systems can measure the expression level of thousands of genes simultaneously, providing a massively-parallel affinity-based detection platform in life science research. Unfortunately, the uncertainty originating from both inherent noise sources and systematic errors in each experiment can obscure some of the important characteristics of the biological processes of interest. The expression level uncertainty (overall measurement error) in microarrays, can originate from the probabilistic characteristics of detection process as mentioned before, all the way from sample extraction and mRNA purification to hybridization and fluorescent intensity measurements. Currently, there are various techniques which attempt to increase the accuracy and signal-to-noise ratio (SNR) of the estimated values. Nonetheless, these techniques often rely on comparative methods, redundant spots, or mathematical algorithms which introduce confidence zones by excluding the unreliable data and outliers. Independent of the method utilized, the degree in which the SNR can be improved in such approaches can still be limited by the inherent microarray noise and systematic errors.

The interfering signals originating from non-specific bindings in microarrays are generally referred to as “background signals.” Traditionally in microarray analysis, background signals and their fluctuations are all considered as corruptive noise without any signal content. Users often implement a sub-optimal yet widely adopted approach. This technique defines a confidence threshold level for the signal intensity in view of the background, which effectively divides the signals into irrelevant (below threshold) and relevant (above threshold) regimes. This particular approach is theoretically valid and optimal only when there is a global background signal which is constant everywhere. In practical microarray experiments, this assumption may not be not valid since the background and fluctuation level varies between spots. The approach can thus be sub-optimal. Even when local background subtraction methods are employed, the intensity data are sub-optimally processed, as the background signal that is present in the immediate vicinity of a given microarray probe spot may not actually be the same as the background signal from within the spot. The major outcome of background subtraction, regardless of the method that is used, is that the minimum detectable level (MDL) is higher than necessary. It also contributes more errors in ratio analysis approaches, since low level signals are basically truncated away. Both of these effects in turn can reduce the microarray detection dynamic range.

Beside all the uncertainties within the measurement results, there is also one major question in microarrays and all essentially affinity-based biosensor systems, and that is of the necessary incubation time (hybridization time for DNA microarrays). Since the incubation kinetics in the microarrays experiments is a function of analyte diffusion, reaction chamber size, temperature and binding kinetics of every analyte species, as well as the unknown analyte concentrations, the settling time of the system is quite complex and unpredictable. Although all these questions can, to some extent, be empirically addressed, they are still major impediments in microarray technology and platform-to-platform inconsistencies can be caused by them.

In conventional fluorescent-based microarrays and other extrinsic reporter-based (label-based) biosensors assays, the detection of captured analytes is usually carried out after the incubation step. In some cases, proper fluorescent and reporter intensity measurements are compromised in the presence of a large concentration of floating (unbound) labeled species in the incubation solution, whose signal can overwhelm the target-specific signal from the captured targets. When the incubation is ceased and the solution is removed from the surface of the array, the washing artifacts often occur that make the analysis of the data even more challenging. Thus there exists a need for affinity based sensors that are able to simultaneously obtain high quality measurements of the binding characteristics of multiple analytes, and that are able to determine the amounts of those analytes in solution.

SUMMARY OF THE INVENTION

Many of the microarrays currently used in biological and medical research are DNA microarrays, in which the probe that is spotted or synthesized onto a solid surface is DNA. However, in addition to nucleic acids, microarray technologies are applicable to other types of biochemical compounds and analytes that can be immobilized on solid surfaces, such as proteins, carbohydrates, and lipids. Microarrays can be used to study the interactions between compounds of a same or different type (for example, protein-protein interactions, or protein-carbohydrate interactions).

Currently, various homogeneous (closed-tube) assays are available for PCR. These assays detect the target amplicons (i.e., Quantitative PCR or QPCR). Nevertheless, the number of different nucleic acid sequences that can be simultaneously amplified and detected is very limited. Typically, an individual reaction chamber (or well) where the target is amplified and detected contains only a single amplicon. Multiplexed QPCR, defined as the process of amplifying and detecting a plurality of nucleic acid sequences simultaneously in a single reaction chamber, is generally practical only for a small number of amplicons.

PCR relies on an enzymatic replication process in each of its temperature-regulated cycles (typically, 30-40). A PCR cycle typically consists of three distinct phases: denaturing, annealing, and extension. Ideally, at the end of the extension phase, there are twice as many double-stranded target DNA fragments as there were at the beginning of the cycle. This implies an exponential growth of the amount of the target DNA as one proceeds through the cycles. However, practical issues affect the replication process adversely and the efficiency of PCR, defined as the probability of generating a replica of each template molecule, is usually smaller than the desired factor of two.

Quantification of the amplified targets in PCR is typically based on measuring the light intensity emanating from fluorescent reporter molecules incorporated into the double-stranded DNA copies of the target. The measured light intensity is an indication of the actual number of the amplified targets. Some of the commonly used probes are SYBR Green, hybridization, and TaqMan probes. SYBR Green I is a dye whose fluorescence increases significantly upon binding to (intercalating) double-stranded DNA. SYBR Green is non-discriminatory and will bind to non-specific byproducts of PCR (such as the primer-dimers). For this reason, special attention needs to be paid to optimizing the conditions of PCR with SYBR Green reporters. Hybridization probes are specific to the target DNA sequence. A hybridization probe typically consists of two short probe sequences, one labeled with a fluorescence resonance energy transfer donor and the other with an acceptor dye. The two probe sequences can be designed such that they hybridize next to each other on the target sequence; the co-location of the donor and the acceptor initiates energy transfer and, therefore, the change in their respective light intensities indicates successful replication of the target. The TaqMan probes are also specific to the target sequence, and are designed so that they contain a fluorescent dye in the vicinity of a quenching dye. Where the TaqMan probe hybridizes to the template, and the template is replicated, the TaqMan probe is degraded by the exo activity of the polymerase, separating the fluorescent dye from the quenching dye, resulting in an increased fluorescent signal.

In Q-PCR, fluorescent signal is measured at the end of each temperature cycle. The measured light intensities create a reaction profile, which can be plotted against the number of cycles and used to determine the concentration of the nucleic acid sequence that was amplified.

Attempts at employing QPCR for the simultaneous amplification and detection of many target amplicons in a single well are plagued with practical issues that present obstacles to achieving a truly multiplexed Q-PCR. A common approach used is to divide the biological sample of interest into equal-sized quantities which are then mechanically delivered into separate wells (typically, 96, 192, or 384). This type of sample splitting reduces the amount of material in each individual amplification well, creating issues of sample size, and necessitating precise sample distribution across the wells.

On the other hand, high-throughput screenings of multiple target analytes in biological samples is typically obtained by exploiting the selective binding and interaction of recognition probes in massively-parallel affinity-based biosensors, such as microarrays. Gene expression microarrays, for example are widely used microarray platforms. These systems measure the expression level of thousands of genes simultaneously.

To increase the quality of microarray data, real-time microarray (RT-μArray) systems have been developed. These systems can evaluate the abundance of a plurality of target analytes in the sample by real-time detection of target-probe binding events. To achieve this, RT-μArrays employ a detection scheme that is a major departure from the techniques typically used in conventional fluorescent-based microarrays and other extrinsic reporter-based biosensors assays. In the latter, the detection of captured analytes is carried out after the hybridization (incubation)-step. This is due to the characteristics of the assays used therein, which require removing the solution during the fluorescent and reporter intensity measurements that are done either by scanning and/or various other imaging techniques. This limitation is due in part to the high concentration in solution of unbound labeled species which can overwhelm the target-specific signal from the captured targets. Furthermore, when the hybridization is ceased and the solution is taken away from array surface, washing artifacts typically occur which can make the analysis of the data challenging.

Thus, while Q-PCR provides a convenient and accurate method for measuring the amount of nucleic acid sequences in a sample, it is limited to a single sequence or a small number of sequences in a single fluid volume. And while microarray technology provides for measuring over hundreds of thousands of sequences simultaneously, conventional arrays are not amenable to the type of detection required for practical multiplexed Q-PCR. Thus there exists a strong need for methods and systems for performing multiplex Q-PCR to accurately measure the presence and/or amount of multiple nucleic acid sequences in a single fluid volume in a single amplification reaction.

Affinity-based biosensors exploit selective binding and interaction of certain bio-molecules (recognition probes) to detect specific target analytes in biological samples. The essential role of the biosensor platforms and the parallel and miniaturized version of them as microarrays may include exploiting specific bindings of the probe-target complexes to produce detectable signals, which correlate with the presence of the targets and conceivably their abundance. The essential components of such a system may include the molecular recognition layer (capturing probes) integrated within or intimately associated with a signal-generating physiochemical transducer and a readout device.

To generate target-specific signal, the target analytes in the sample volume generally first need to collide with the recognition layer, interact with the probes, bind to the correct probes, and ultimately take part in a transduction process. The analyte motion in typical biosensor settings (e.g., aqueous biological buffers) can be dominated by diffusion spreading, which from a microscopic point of view is a probabilistic mass-transfer process (modeled as a random walk for each analyte molecule). Accordingly, analyte collisions with probes may become a stochastic process. Moreover, because of the quantum-mechanical nature of chemical bond forming, the interaction between the probes and the analytes molecules may also be probabilistic, thus further contributing to uncertainty and noise corruption of the measured data in biosensors and microarrays. Such phenomena may be viewed as inherent noise in the detection system, which may result in unavoidable uncertainties even when the measurements are noiseless. Such inherent noise may be essentially inevitable since it may originate from the stochastic nature of molecular-level interactions. Its examples include Poisson noise sources in microarrays and image sensor detection shot-noise.

Beside the inherent noise, other non-idealities may also corrupt the signal obtained by the microarray experiments. Examples of such phenomena include probe density variations, sample preparation systematic errors, and probe saturation. In some cases, systematic errors may be defined as the unwanted deviations from the intended detection procedure. If these errors are accurately evaluated, they can be compensated by post experiment data processing.

Gene expression microarrays are a widely used microarray platform. These systems can measure the expression level of thousands of genes simultaneously, providing a massively-parallel affinity-based detection platform in life science research. Unfortunately, the uncertainty originating from both inherent noise sources and systematic errors in each experiment can obscure some of the important characteristics of the biological processes of interest. The expression level uncertainty (overall measurement error) in microarrays, can originate from the probabilistic characteristics of detection process as mentioned before, all the way from sample extraction and mRNA purification to hybridization and fluorescent intensity measurements. Currently, there are various techniques which attempt to increase the accuracy and signal-to-noise ratio (SNR) of the estimated values. Nonetheless, these techniques may often rely on comparative methods, redundant spots, or mathematical algorithms which introduce confidence zones by excluding the unreliable data and outliers. Independent of the method utilized, the degree in which the SNR can be improved in such approaches can still be limited by the inherent microarray noise and systematic errors.

The interfering signals originating from non-specific bindings in microarrays may be generally referred to as “background signals.” Traditionally in microarray analysis, background signals and their fluctuations are all considered as corruptive noise without any signal content. Users often implement a sub-optimal yet widely adopted approach. This technique may define a confidence threshold level for the signal intensity in view of the background, which effectively divides the signals into irrelevant (below threshold) and relevant (above threshold) regimes. This particular approach is theoretically valid and optimal only when there is a global background signal which is constant everywhere. In practical microarray experiments, this assumption may not be valid since the background and fluctuation level varies between spots. The approach can thus be sub-optimal. Even when local background subtraction methods are employed, the intensity data are sub-optimally processed, as the background signal that is present in the immediate vicinity of a given microarray probe spot may not actually be the same as the background signal from within the spot. The major outcome of background subtraction, regardless of the method that is used, is that the minimum detectable level (MDL) is higher than necessary. It also contributes more errors in ratio analysis approaches, since low level signals are basically truncated away. Both of these effects in turn can reduce the microarray detection dynamic range.

Beside all the uncertainties within the measurement results, there is also one major question in microarrays and all essentially affinity-based biosensor systems, and that is of the necessary incubation time (hybridization time for DNA microarrays). Since the incubation kinetics in the microarrays experiments is a function of analyte diffusion, reaction chamber size, temperature and binding kinetics of every analyte species, as well as the unknown analyte concentrations, the settling time of the system is quite complex and unpredictable. Although all these questions can, to some extent, be empirically addressed, they are still major impediments in microarray technology and platform-to-platform inconsistencies can be caused by them.

One aspect of the invention is a method comprising measuring binding of analytes to probes on a microarray in real-time. In one embodiment, the method comprises the steps of: contacting a fluid volume comprising a plurality of different analytes with a solid substrate comprising a plurality of different probes, wherein the probes are capable of specifically binding with the analytes; and measuring signals at multiple time points while the fluid volume is in contact with the substrate, wherein the signals measured at multiple time points can be correlated with the amount of binding of the analytes with the probes. One embodiment of the method further comprises using the signals measured at multiple time points to determine the concentration of an analyte in the fluid volume. In some embodiments, a change in the signals with time correlates with the amount of the analytes bound to the probes.

In some embodiments, the signals comprise electrochemical, electrical, mechanical, magnetic, acoustic, or electromagnetic signals. In some embodiments, the signals are electromagnetic signals comprising fluorescence, absorption, or luminescence. In some embodiments, the analytes comprise quenching moieties, and the electromagnetic signals measured at multiple time points correlate, at least in part to the quenching of fluorescence. In some embodiments, the fluorescence that is quenched is due at least in part to fluorescent moieties bound to the probes. In some embodiments, the fluorescence that is quenched is due at least in part to fluorescent moieties bound to the solid substrate, wherein such fluorescent moieties are not covalently bound to the probes. In some embodiments, the fluorescence that is quenched is due at least in part to fluorescent moieties that are non-covalently bound to the probe. In some embodiments, the optical signals measured at multiple time points are due, at least in part, to fluorescent resonance energy transfer (FRET).

In some embodiments, the different probes are located on the solid substrate at different addressable locations. In some embodiments there are at least about 3, 4, 5 10, 50, 100, 500, 1000, 10,000, 100,000, or 1,000,000 probes. In some embodiments, the solid substrate comprises one or more beads.

In some embodiments, the analytes and/or the probes comprise the chemical species of nucleic acids or nucleic acid analogs, proteins, carbohydrates, or lipids. In some embodiments, the analytes and the probes are the same type of chemical species. In some embodiments, the analyte and the probe are each a different type of chemical species. In some embodiments, the analyte and the probe comprise nucleic acids or nucleic acid analogs. In some embodiments, the probes comprise proteins, which in some cases can comprise antibodies or enzymes.

In some embodiments, the at least two time points are measured at a time when the amount of binding of an analyte to a probe corresponding to that signal is less than 50% of saturation.

In some embodiments, two or more time points are measured when the fluid volume is at one temperature, and two or more time points are measured when the fluid volume is at a second temperature. In some embodiments, two or more time points are measured when the analyte in the fluid volume is at one concentration, and two or more time points are measured when the fluid volume is at a second concentration. In some embodiments, the concentration of the analyte is enriched between the sets of time points. In some embodiments, the concentration of the analyte is diluted between the sets of time points.

In some embodiments, the solid substrate also comprises control spots.

In some embodiments, the method comprises the use of multiple fluorescent species, with different excitation and/or emission spectra. In some embodiments, the method comprises the use of multiple quencher species, with different quenching properties.

In some embodiments the method further comprises determining binding of a probe with two or more analytes comprising subjecting binding data corresponding to signal and time to an algorithm which determines the contribution of each of the two or more analytes to the binding data. In some embodiments, the probes comprise a fluorescent moiety and the initial surface concentration of probes is determined by measuring fluorescence.

One aspect of the invention is a method of claim 2 wherein: (i) the analytes comprise nucleic acid molecules labeled with a quencher; (ii) the probes comprise nucleic acid molecules; (iii) the substrate is substantially planar and comprises an array of discrete locations at different addresses on the substrate, wherein the locations have attached thereto different probes and a fluorescent label that produces the signal, wherein the fluorescent label is in sufficient proximity to the probe whereby hybridization between an analyte and probe at the location causes FRET and/or quenching of the signal. In some embodiments, the fluorescent label is attached to the surface through the probe. In some embodiments, the fluorescent label is non-covalently attached to the probe. In some embodiments, the fluorescent label is not attached to the surface through the probe. In some embodiments, the concentration of the analyte in the fluid based on the kinetics of change of the signal over time.

In some embodiments of the method of the invention, the fluid volume further comprises competitor molecules labeled with a quencher, wherein the competitor molecules compete with the analytes for binding with the probes.

One aspect of the invention is a method of detecting binding between analyte molecules and an array of probe molecules comprising: (a) incubating the analyte molecules with the array of probe molecules, wherein binding between a analyte molecule and a probe molecule results in a change in a signal from the array; and (b) measuring the signal from the array over time during incubation. In some embodiments, binding between a target molecule and a probe molecule results in a decrease in a signal from the array. In some embodiments, binding between a target molecule and a probe molecule results in an increase in a signal from the array.

One aspect of the invention is a method of detecting binding between an analyte molecule and a probe comprising: (a) incubating an analyte molecule comprising a quencher of a donor-quencher pair with a probe immobilized on a surface of a solid substrate under conditions whereby the analyte molecule can bind to the probe, wherein the donor of the donor-quencher pair is immobilized on the surface at a distance from the immobilized probe and whereby binding between the analyte molecule and the probe quenches a signal from the donor, and wherein the donor is not directly coupled to the immobilized probe; and (b) measuring the signal. In some embodiments, the method comprises incubating a plurality of different analyte molecules with a plurality of different probes immobilized to different addressable locations on the surface of the substrate.

One aspect of the invention is a system comprising: (a) a device with (i) a solid support having a surface and (ii) a plurality of different probes, wherein the different probes are immobilized to the surface; (b) a fluid volume comprising an analyte wherein the fluid volume is in contact with the solid support, and (c) a detector assembly comprising means to detect signals measured at multiple time points from each of a plurality of spots on the microarray while the fluid volume is in contact with the solid support. In some embodiments, the signals measured at multiple time points detected by the detectors can be correlated with the binding of analyte to the probes.

In some embodiments the system further comprises: (d) an assembly that controls temperature of the solid support and/or the fluid volume. In some embodiments, the different probes are immobilized at different addressable locations.

In some embodiments the system further comprises: (e) a data acquisition system for acquiring and storing the data and (f) a computing system for analyzing the signals. In some embodiments, the plurality of detectors comprises an array of transducers. In some embodiments, the array of transducers is capable of measuring an electrochemical, electrical, mechanical, magnetic, acoustic, or optical signal. In some embodiments, the solid substrate is in contact with the array of transducers. In some embodiments, the transducer array spaced away from the solid substrate. In some embodiments, one or more transducers correspond to an addressable location. In some embodiments, the transducer array is an optical transducer array which is optically coupled to the solid substrate. In some embodiments, the optical transducer array is optically coupled to the solid substrate via one or more lenses.

In some embodiments, the system is capable of measuring a plurality of binding rates simultaneously. In some embodiments, the plurality of binding rates is used to determine the concentration of a plurality of analytes.

In some embodiments, the signal detected by the detector comprises an electrochemical, electrical, mechanical, magnetic, acoustic, or optical signal. In some embodiments, the signal is generated from cyclic voltammetry, impedance spectroscopy, or surface plasmon resonance systems. In some embodiments, the signal is an optical signal. In some embodiments, the signal is from fluorescence, absorption, or luminescence. In some embodiments, the signals measured at multiple time points, correlating to the binding of analyte are due, at least in part, to fluorescent resonance energy transfer (FRET). In some embodiments, the signals measured at multiple time points, correlating to the binding of analyte are due, at least in part, to quenching of a fluorescent signal. In some embodiments, the signals measured at multiple time points are due, at least in part, to the interaction between an analyte comprising a quenching moiety, and probe comprising a fluorescent moiety. In some embodiments, the moiety comprising the optical signal is covalently bound to the probe molecule. In some embodiments, the moiety comprising the optical signal is non-covalently bound, to the probe molecule. In some embodiments, the moiety comprising the optical signal is bound to the probe molecule through another molecule. In some embodiments, the moiety comprising the optical signal is bound to the substrate.

One aspect of the invention is a system comprising: an assay assembly comprising means to engage a microarray and means to perform an assay on a surface of the microarray; and a detector assembly comprising means to detect signals measured at multiple time points from each of a plurality of spots on the microarray during the performance of the assay. In some embodiments, the means to perform the assay comprise means to provide a compartment wherein the surface of the microarray comprises a floor of the compartment and means to deliver reagents and analytes into the compartment.

One aspect of the invention is a device comprising: a solid substrate having a surface and a plurality of different probes, wherein the different probes are immobilized to the surface at different addressable locations, the addressable locations comprise optical signal moieties bound to the surface, the optical signal moieties are not bound directly to the probes, and the optical signal from the optical signal moieties is capable of changing upon binding of an analyte to the probes. In some embodiments, the optical signal moiety comprises a dye, a luminescent moiety, or a fluorescent moiety.

One aspect of the invention comprises software comprising: (a) a computer executable code that accesses information about signals measured at multiple time points at each of a plurality of known locations on a microarray, wherein the signal intensity is a function of the number of binding events between analyte molecules and probe molecules attached to the microarray at known locations. In some embodiments, the software further comprises: (b) code that executes an algorithm that uses the information to determine the expected number of binding events before binding has reached saturation, the existence and number of analyte molecules in the solution and the existence of cross-hybridization. The algorithm furthermore can suppress the effects of cross-hybridization on the acquired data.

Another aspect of the present disclosure provides a system for determining at least one parameter associated with a binding interaction between at least one analyte and at least one probe, comprising: a substrate comprising a surface having the at least one probe coupled to the surface, wherein the at least one probe comprises a donor that provides a fluorescence signal; an excitation source that provides an excitation signal to the surface, which excitation signal is sufficient to cause the donor to provide the fluorescence signals; a chamber in fluid communication with the surface, the chamber comprises a fluid volume comprising the at least one analyte under conditions that are sufficient to permit the binding interaction between the at least one analyte and the at least one probe, wherein the at least one analyte comprises an acceptor that comprises a quencher, wherein the binding interaction between the at least one analyte and the at least one probe results in an interaction between the donor and the quencher that decreases intensities of the fluorescence signals of the donor; a detector that detects the fluorescence signals from the surface at multiple time points in real time during the binding interaction, wherein the detector is integrated with the substrate such that the fluorescence signals are detected by the detector at a location below the surface; and a computer system in communication with the detector, wherein the computer system (i) uses the detector to detect decreases in the intensities of the fluorescence signals from the surface at multiple time points in real time during the interaction, (ii) determines the at least one parameter associated with the binding interaction based at least in part on the decreases in the intensities of the fluorescence signals from the surface, and (iii) provides an output indicative of the at least one parameter.

In some embodiments, the system further comprises a data acquisition system that stores the output. In some embodiments, the excitation signal is an electromagnetic signal. In some embodiments, the at least one parameter comprises: a forward binding reaction rate; a backward binding reaction rate; C which is an original quantity of the at least one analyte in the fluid; C−(P_(o)−P(t)) which is an available analyte density at time t, wherein P_(o) is a number of unbound molecules of the at least one probe, and wherein P(t) is a number of unbound molecules of the at least one probe at time t; t which is a time constant; P_(∞) which is a steady-state value of P(t); n(t), which is a number of analytes in the fluid volume that are specific to the probe molecule; P_(near), which is a probability that the at least one analyte is in close proximity to the probe molecule; P_(h), which is a probability that, in a unit interval of time, the at least one analyte binds to the probe once the analyte is near; P_(r), which is a probability that, in a unit interval of time, the at least one analyte bound to the probe molecule is released; N, which is a total number of analyte molecules; q(t), which is a number of unbound molecules of the at least one analyte as a function of time; a reaction rate between the at least one analyte and the at least one probe; or a cross-hybridization parameter. In some embodiments, the substrate comprises a plurality of different probes coupled to the surface. In some embodiments, the fluid volume comprises a plurality of different analytes, including the at least one analyte. In some embodiments, the acceptor is a quencher. In some embodiments, the at least one analyte is not labeled with a metal cluster. In some embodiments, the computer system receives electrical signals corresponding to the signals from the detector while the fluid volume is in contact with the surface. In some embodiments, the computer system receives the electrical signals corresponding to the signals from the surface over a time period in which the fluid volume that is in contact with the surface is not washed. In some embodiments, the surface comprises a plurality of probe spots, and a given probe spot of the plurality of probe spots includes the at least one probe. In some embodiments, the excitation source and the detector are disposed adjacent to a same side of the substrate. In some embodiments, the fluid volume further comprises a plurality of different analytes. In some embodiments, the system further comprises a temperature controller, wherein the temperature controller changes a temperature of the fluid and/or the substrate.

INCORPORATION BY REFERENCE

All publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.

BRIEF DESCRIPTION OF THE DRAWINGS

The novel features of the invention are set forth with particularity in the appended claims. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative embodiments, in which the principles of the invention are utilized, and the accompanying drawings of which:

FIG. 1 shows conventional detection procedure in affinity-based biosensors where capturing probes are used to capture target analyte in the incubation phase, and detection is carried out in a dry-phase after completion of the incubation.

FIG. 2 shows conventional detection after completing incubation at time t₁ and the uncertainty associated with it.

FIG. 3 shows that in real-time microarray systems of the present disclosure, multiple measurement of the number of captured analytes can be carried out, without the necessity of stopping the incubation step.

FIG. 4 shows a block diagram of the errors associated with conventional DNA microarrays.

FIG. 5 shows a nucleic acid based real-time microarray system of the present disclosure where the probes are labeled with fluorescent moieties.

FIG. 6 shows a nucleic acid based real-time microarray system of the present disclosure where the probes are labeled with fluorescent moieties, the analytes are labeled with quenchers, and the fluorescent intensity on various spots can be used to measure the amount of analyte specifically bound to probe.

FIG. 7 shows a block diagram of a real-time microarray system of the present disclosure.

FIG. 8 shows an example of a real-time microarray system An example of a real-time microarray system where binding of BHQ2 quencher-labeled cDNA molecules were detected using a fluorescent laser-scanning microscope.

FIG. 9 shows a real-time microarray system where the detection system comprises a sensor array in intimate proximity of the capturing spots.

FIG. 10 shows the layout of a 6×6 DNA microarray of the present disclosure

FIG. 11 shows a few samples of the real-time measurements of the microarray experiment where control target analytes are added to the system

FIGS. 12-15 each show data for 4 different spots with similar oligonucletide capturing probes. The target DNA analyte is introduced in the system at time zero and quenching (reduction of signal) occurs only when binding happens.

FIG. 16 shows the signals measured during two real-time experiments wherein a target analyte (target 2) is applied to the microarray, at 2 ng and at 0.2 ng.

FIG. 17 shows the signal versus time measured in a real-time oligonucleotide array, and the fit of the data to an algorithm, where 80 ng/50 μl of the target is applied to the array.

FIG. 18 shows he signal measured in a real-time oligonucleotide array, and the fit of the data to an algorithm, where 16 ng/50 μl of the target is applied to the array.

FIG. 19 shows the results of a simulation indicating the potential of suppression of cross-hybridization over 3 orders of magnitude.

FIG. 20 illustrates an embodiment of the disclosure wherein primers (P1, P2) with quenchers (Q1, Q2) are incorporated into amplicons in an amplification reaction, allowing the amplicons to be detected in real-time by hybridization with probes on an array resulting in quenching of the fluorescence of fluorescent moieties (F1, F2) attached to the probes. The measurement of amplicons after multiple amplification cycles can be used to determine the concentration of the starting target nucleotide sequence (A and/or B).

FIG. 21 shows how, for the embodiment shown in FIG. 20, primers (P1, P2) with quenchers (Q1, Q2) can, in some instances, hybridize to the 3′ end of amplicons that are hybridized to probes (C′, D′) on the array.

FIG. 22 illustrates an embodiment of the disclosure in which the probes (P1, P2) and amplicons are designed such that a primer with a quencher (Q1, Q2) hybridizes to the 3′ end of an amplicon which is hybridized to a probe on an array, resulting in quenching of the fluorescence of a fluorescent moiety (F1, F2) attached to the probe.

FIG. 23 illustrates an embodiment of the disclosure in which quenchers (Q) are incorporated into amplicons during the amplification reaction by using a d-NTP containing a quencher in the amplification. The quencher-labeled amplicons are detected in real-time by hybridization to probes on an array resulting in quenching of fluorescent moieties (F) attached to the array. The measurement of amplicons after multiple amplification cycles can be used to determine the concentration of the starting target nucleotide sequence (A and/or B).

FIG. 24 shows how, in some embodiments of the disclosure, the fluorescent moieties (F) are bound to the surface of the array, but are not covalently bound to the probes. The fluorescent moieties can be bound directly or attached to another molecule bound to the surface. The surface bound fluorescent moieties can be quenched upon hybridization of amplicons containing quenchers (Q) to probes on the array, allowing the measurement of amplicon hybridization in real time.

FIG. 25 shows an embodiment of a temperature cycle of the present disclosure where the temperature Cycle has 5 phases.

FIG. 26 illustrates an example of a conventional microarray.

FIG. 27 displays an example of microarray technology based upon fluorescent detection.

FIG. 28 demonstrates a passive pixel sensor (PPS), an active pixel sensor (APS), and a digital pixel sensor (DPS) for use as the pixel architecture of a complementary metal oxide semiconductor (CMOS) image sensor array.

FIG. 29 shows an example of a sample complementary metal-oxide-semiconductor (CMOS) of the present disclosure.

FIG. 30 illustrates an embodiment of the disclosure comprising a fiber optic faceplate (FOF).

FIG. 31 shows a block diagram of some of the components of systems of the present disclosure.

FIG. 32 illustrates an embodiment of a system comprising an assay kit, a disposable sensor chip, a computer chip reader and software for executing a method of the disclosure.

FIG. 33 illustrates the absorption and emission spectra of Cy3 molecule.

FIG. 34 demonstrates an example design of a system of the disclosure comprising a capacitive transimpedance amplifier (CTIA).

FIG. 35 shows the die photo and the I/O pin allocation of an integrated 7 by 8 pixel biosensor array.

DETAILED DESCRIPTION OF THE INVENTION Introduction

The methods, devices, and systems disclosed herein concern the real-time measurements of target binding events in microarrays and parallel affinity-based biosensors. The methods and systems described herein can be referred to as real-time microarray (RT-μArray) systems. Real-time measurement of the kinetics of multiple binding events allows for an accurate and sensitive determination of binding characteristics or of analyte concentration for multiple species simultaneously. Real-time measurements also allow for the rapid determination of the amount of analyte present in a fluid, because the measurement can be made without waiting for saturation of binding. Real-time microarray systems are described in the U.S. Pat. No. 9,133,504, which is entirely incorporated herein by reference.

One aspect of the present disclosure provides performing a PCR amplification in a solution in contact with a probe array, where the solution contains nucleotide sequences of interest. The probes are bound to the array at independently addressable locations and have fluorescent moieties. The probes are designed to specifically hybridize with target analytes (e.g., amplicons generated by the PCR), and the target analytes are designed such that hybridization of the target analytes to the probe results in quenching of the fluorescent signals from the probes. During each cycle of PCR, hybridization between amplicon and probe is detected, and the denaturing step of PCR releases the amplicons for continued amplification. Preferably, the hybridization is measured in real-time during hybridization of target analytes to probes, producing kinetic measurements that can be used to determine the amount of target analytes in solution. Performing the measurement over many cycles allows the measurement of the build-up of amplicon as a function of amplification cycle, which can be extrapolated back in order to determine the concentration of the nucleotide sequence in the sample. The determination of the amount of nucleotide sequence by amplicon build-up is analogous to a CT measurement using Q-PCR, but the present invention, being in an array format, allows for a multiplex assay.

In one aspect of the present disclosure, rather than having the fluorescent moieties that are quenched by the target analytes attached to the probe, the fluorescent moieties are attached to the surface within the independently addressable location of the probe. While the fluorescent moiety is not covalently bound to the probe, the fluorescence can still be quenched upon hybridization. This aspect allows for the measurement of target analyte-probe binding without the need for synthesizing fluorescently labeled probes.

In some embodiments, the amplification method that is used is quantitative-PCR or Q-PCR. In Q-PCR, a PCR reaction is carried out to amplify a nucleotide sequence. The amount of amplicon produced is measured at the end of each amplification cycle. After a number of amplification cycles, the amount of nucleic acid in the original sample can be determined by analyzing the build-up of amplicon over the number of amplification cycles. Q-PCR allows for the determination of the presence or the amount very small amounts of sample, in some cases, down to the detection of a single molecule. While Q-PCR is a valuable technique for measuring nucleic acid sequences, the ability to measure multiple sequences at a time in a single fluid with Q-PCT reaction is limited. The present invention utilizes an array of multiple nucleic acids, thus allowing for the measurement of the presence or amount of multiple nucleic acid sequences in the same sample during the same Q-PCR amplification reaction. In some embodiments, the present invention allows for the determination of more than about 3, 5, 10, 100, 1000, 10,000, 100,000, 1,000,000 or more nucleic acid sequences in the same sample during the same amplification reaction.

The term “quantitative-PCR” or “Q-PCR” as used herein to refer to the process that is also referred to outside of this application as “real-time PCR”. The term “Q-PCR” as used herein encompasses both the qualitative and quantitative determination of nucleic acid sequences. Q-PCR involves the measurement of the amount of amplicon as a function of amplification cycle, and using this information in order to determine the amount of the nucleic acid sequence corresponding to the amplicon that was present in the original sample. The Q-PCR process can be described in the following manner. A PCR reaction is carried out with a pair of primers designed to amplify a given nucleic acid sequence in a sample. The appropriate enzymes and dNTP's are added to the reaction, and the reaction is subjected to a number of amplification cycles. The amount of amplicon generated from each cycle is detected, but in the early cycles, the amount of amplicon can be below the detection threshold. The amplification can be seen as occurring in two phases, an exponential phase, followed by a non-exponential plateau phase. During the exponential phase, the amount of PCR product approximately doubles in each cycle. As the reaction proceeds, however, reaction components are consumed, and ultimately one or more of the components becomes limiting. At this point, the reaction slows and enters the plateau phase (generally between cycles 28-40). Initially, the amount of amplicon remains at or below background levels, and increases are not detectable, even though amplicon product accumulates exponentially. Eventually, enough amplified product accumulates to yield a detectable signal. The cycle number at which this occurs is called the threshold cycle, or CT. Since the CT value is measured in the exponential phase when reagents are not limited, Q-PCR can be used to reliably and accurately calculate the initial amount of template present in the reaction. The CT of a reaction is determined mainly by the amount of nucleic acid sequence corresponding to amplicon present at the start of the amplification reaction. If a large amount of template is present at the start of the reaction, relatively few amplification cycles will be required to accumulate enough product to give a fluorescent signal above background. Thus, the reaction will have a low, or early, CT. In contrast, if a small amount of template is present at the start of the reaction, more amplification cycles will be required for the fluorescent signal to rise above background. Thus, the reaction will have a high, or late, CT. The present invention allows for the measurement of the accumulation of multiple amplicons in a single fluid in a single amplification reaction, and thus the determination of the amount of multiple nucleic acid sequences in the same sample with the methodology of Q-PCR described above.

In some embodiments the Q-PCR can incorporate a blocker. For example, a sequence that is complementary to the nucleotide sequence being amplified can act as a blocker by blocking the synthesis of the amplicon. Blockers that are sensitive to small changes in nucleotide sequence can be used, for example, for single nucleotide polymorphism (SNP) determination. In some embodiments, the blocker is made from a non-natural nucleic acid with different, for example, stronger, hybridization characteristics. In some embodiments the blocker is made from locked nucleic acid (LNA) or protein nucleic acid (PNA).

In the current invention, the amplification is carried out in a fluid that is in contact with an array comprising multiple nucleic acids probes, each nucleic acid probe attached to an independently addressable location. An independently addressable location is a region of the array that can be addressed by a detector to obtain information about amplicon binding to that specific region. The multiple amplicons that are generated can each bind specifically to one or more nucleic acid probes bound to the array, and the rate of binding of the amplicons to the nucleic acids is measured in real-time to determine the amount of the amplicon in the fluid. As with Q-PCR, the sample can be subjected to multiple amplification cycles, and the amount of amplicon during or after the cycles can be measured. At the end of multiple amplification cycles, the build-up of amplicon as a function of amplification cycle can be determined, and can be used to determine the presence or amount of the nucleic acid sequences present in the original sample. This method allows the measurement of the presence or amount of tens to hundreds to millions of different nucleotide sequences in the same sample during a single amplification. This type of analysis is not practical on conventional microarrays that require hybridizations to reach saturation, require washing and drying of the array before detection, and often require a separate labeling step. The real-time arrays of the present disclosure allow for this multiplex Q-PCR because the fluid need not be removed from the array to detect the amplicons, and because the measurement of the amount of amplicon can be carried out rapidly without waiting for saturation of binding.

In some embodiments of the present disclosure, fluorescent resonance energy transfer (FRET) and/or quenching of fluorescence is used in order to determine the amount of amplicon present in the solution. For example, primers in a PCR amplification reaction are labeled with a quencher, and the nucleic acid probes on the array are labeled with a fluorescent moiety that is quenched upon binding of the amplicon to the nucleic acid probe. As the PCR amplification proceeds, the quenchers are incorporated into the amplicons formed in the amplification. During or after the temperature cycles of the PCR reaction, the decrease in the fluorescent signal with time from the probes is measured in real-time to determine the rate of binding of the amplicon to the probe which is used to determine the amount of amplicon in solution. The values obtained for the amount of amplicon as a function of amplification cycle can then be used to calculate the presence or amount of the nucleotide sequences corresponding to the amplicons in the original sample. FIGS. 20-24, described in more detail below, show embodiments of the disclosure that utilize FRET and quenching. The use of quenchers rather than fluorescently labeled amplicons in solution has the advantage that it minimizes the fluorescent background of the solution, thus increasing the quality of the measurement of the fluorescence at the surface. Because the different nucleic acid probes on the surface are at differently addressable locations on the surface, the binding of multiple amplicons to multiple probes can be determined in the same amplification reaction. The disclosure thus provides a multiplex Q-PCR system that can determine the presence or concentration of about 2, 3, 4, 5, 6, 8, 10, 20, 30, 50; 100, 200, 500, 1,000, 10,000, 100,000, 1,000,000 or more nucleotide sequences in the same fluid in same amplification reaction.

While a conventional multiplex Q-PCR allows the measurement of a small number of nucleic acid sequences in the same fluid by using dyes of different wavelengths, it has disadvantages, and is limited to a small number of amplicons. The current method carrying out multiple Q-PCR reactions on a sample, especially for larger numbers of amplicons greater than 5 or 8 is to split the sample containing the nucleotide sequence into multiple samples, and perform Q-PCR on all of the samples in parallel. This method has the disadvantages of uncertainties due to sample splitting, and that a larger sample may be needed in order to have enough material in each of the split samples. Thus, the present disclosure provides a unique multiplex Q-PCR system allowing for the determination of the concentration or presence of about 10 or more, about 20 or more, or about 50 or more nucleotide sequences in the same fluid in the same amplification reaction.

FIG. 20 illustrates an embodiment of the disclosure in which the primers have attached quenchers such that the quenchers become incorporated into the amplicons. In FIG. 20, the sample comprises a double stranded DNA, having complementary strands A and B. The sample is amplified using two primers of a primer pair (P1 and P2) each primer comprising a quencher (Q1 and Q2). In some embodiments, Q1 and Q2 will be the same quencher. In some embodiments, Q1 and Q2 will be different quenchers. In some embodiments, only one member of the primer pair will have a quencher. The primers are chosen so as to amplify the nucleotide region defined by the nucleotide region to which each of the primers are complementary on each of the two strands. The nucleotide sequences of both the A and the B strand are amplified. The double stranded DNA and the primers are then subjected to multiple temperature cycles in the presence of polymerase and dNTP's to generate amplified product, or amplicon. Here, either the generated double stranded DNA or each of the strands of the generated DNA can be referred to as amplicons. The primers comprising the quenchers become incorporated into the amplicons, resulting in amplicons which contain quenchers. Since the primers are incorporated at the 5′ end of the strand that they become incorporated into, the quencher will tend to be at the 5′ end of the amplicon that incorporates the primer. The quencher can be at any location along the primer. The quencher can be at the 3′ end of the primer, at the 5′ end of the primer, or it can be attached to nucleotides in between the ends of the primer.

During the amplification, the temperature phases are controlled to allow the measurement of binding of the generated amplicons to the probes on the array which is in contact with the fluid containing the amplicons. The amplicons can hybridize to the probes on the array as shown in FIG. 20. FIG. 20 shows, for example probe C′ attached to the surface of an array. A portion of the sequence of probe C′ is complementary to a portion of the sequence on amplicon C. The length of overlap illustrated in the figures is not necessarily indicative of the region of overlap between the probe and the amplicon, which can be, for example, from several bases to thousands of bases long.

Typically, as illustrated in the figures, the region of the amplicon that corresponds to the primer (and the primers themselves) will not be complementary to the probe. This design can be useful in preventing primer from binding the probe, which could result in unwanted quenching, and could result in unwanted nucleic acid strands by priming synthesis on the probes.

In this embodiment, probe C′ has a fluorescent moiety attached to it. The fluorescent moiety can be attached at any place along the length of the probe. The hybridization of the probe C′ to the amplicon C brings the quencher Q2 and the fluorescent moiety, F1 into proximity which can result in quenching of fluorescence from F1. The quencher Q2 and the fluorescent moiety F1, and their attachment to the amplicon and probe can be modified using methods known in the art in order to increase the interaction between F1 and Q2 and to increase the effectiveness of quenching.

The decrease in the fluorescence from F1 thus provides a measure of the amount of binding of amplicon C to probe C′, and can thus be used to measure the rate of hybridization of the amplicon C to the probe C′. The measured rate of hybridization can be used to determine the amount of amplicon C in solution. The measurement of the amount of amplicon can be done during or after some or all of the temperature cycles of the amplification, and the values measured for amount of amplicon as a function of temperature cycle can be used to determine the original amount of nucleotide sequence from strand A and or strand B.

In some embodiments, amplicon D, which is complementary to amplicon C can concurrently be measured using probe D′, attached to another independently addressable region of the array. By measuring the concentration of both C and D, complementary amplicon sequences, the reliability of the measurement of amplicon amount, and thus the reliability of the amount of the nucleotide sequences from A and/or B can be increased.

FIG. 21 illustrates that in some embodiments, when amplicon C bind to probe C′ near its 5′ ends, the complementary primer P1 with quencher Q1 can hybridize to the 3′ end of the amplicon C. In some embodiments this binding of primer can be minimized or prevented by controlling the design of the primer, amplicon, and probe or by controlling the stringency conditions such as the temperature. For example, the hybridization temperature can be chosen to allow amplicon to probe binding, but not to allow primer binding. In some embodiments, the components can be selected such that the hybridization of Q1 to C does not affect the quenching of the fluorescence at the surface of array. In other embodiments, the hybridization of Q1 to C can act to further quench the fluorescence at the surface of the array. FIG. 21 shows that primer P2 with quencher Q2 can analogously hybridize to amplicon D, which is hybridized to probe D′.

FIG. 22 shows an embodiment where the Probe C″ is designed to be complementary to a nucleotide sequence on amplicon C near the 3′ region rather than near the 5′ region as in FIGS. 20-21. In this embodiment, primer, amplicon, probe and conditions are chosen such that primer P1 with quencher Q1 is hybridized to the 3′ end of C. The quencher Q1 on primer P1 is brought into proximity of the fluorescent moiety F1 on probe C″, resulting in quenching of fluorescence of F1, and providing a measure of the concentration of the amplicon C. Here, quencher Q2 which is near the 5′ end of C does not participate in quenching. In some embodiments both the quenching from both Q1 and Q2 can be used. FIG. 22 also shows that the same quenching strategy can be used for the complementary amplicon D.

FIG. 23 shows an alternative method of incorporating quenchers into the amplicons. Here, one or more of the dNTP's that will become incorporated into the amplicons has a quencher Q attached. The quenchers thus become incorporated into the formed amplicons. When the amplicons containing the quenchers Q bind to the surface, the probes and amplicons are designed such that the quenchers interact with and quench the fluorescence of the fluorescent moiety F on the surface bound probe. The probe can be complementary to either amplicon C or amplicon D, or the array could incorporate probes to both amplicons C and D. In some embodiments all of the dNTP's of a single type will carry a quencher. In other cases, only a fraction of the dNTP's of a single type will carry a quencher, resulting in the statistical incorporation of quenchers into the amplicons.

FIG. 24 illustrates how, in some embodiments, the fluorescent moiety on the array is not covalently bound directly to the probes, but is bound directly to the surface of the array, or is bound through another species on the surface of the array. In FIG. 24, amplicons with quenchers Q hybridize to the probes on the array, and the quencher Q is brought into proximity of the fluorescent moiety on the surface, resulting in quenching that can be used as a measure of the amount of amplicons hybridized to the probes. This aspect of the disclosure can be useful in that having the fluorescent moiety attached directly to the surface can simplify manufacturing, which can improve costs, and improve the reliability of the system. For example, in some embodiments, one might be required to synthesize fluorescently labeled probe for each spot which can be costly, but by attaching the fluorescent group directly to the surface, no fluorescently labeled probes need be synthesized.

While the embodiments in FIGS. 20-24 describe quenchers and fluorescent moieties, it would be understood by persons of skill in the art that in the above embodiments, any members of a FRET pair could be incorporated into the primers, probes, and/or amplicons in the same manner. The use of quenchers on the species in solution has the advantage that the solution molecules will not create a significant background fluorescence that could interfere with the measurement of surface fluorescence. In some embodiments, the member of the FRET pair attached to the amplicon is fluorescent. In some embodiments, the member of the FRET pair that is attached to the amplicon has an emission spectrum that is different than the member of the FRET pair that is attached to the surface. When the FRET pairs interact upon binding of the amplicon to the probe, in some cases, the interaction will result in a shift in the fluorescence emission peak, for example due to charge transfer between the members of the FRET pair.

One aspect of present disclosure is the evaluation of the abundance of target analytes in a sample by the real-time detection of target-probe binding events. In certain embodiments, RT-μArray detection systems measure the concentration of the target analytes by analyzing the binding rates and/or the equilibrium concentration of the captured analytes in a single and/or plurality of spots. Some applications of RT-μArrays fall within the field of Genomics and Proteomics, in particular DNA and Protein microarrays. Some of the advantages of RT-μArray systems over conventional microarray platforms are in their higher detection dynamic range, lower minimum detection level (MDL), robustness, and lower sensitivity to array fabrication systematic errors, analyte binding fluctuation, and biochemical noise, as well as in the avoidance of the washing step required for conventional microarrays.

One aspect of the disclosure is a method of measuring binding of analytes to a plurality of probes on surface in “real time”. As used herein in reference to monitoring, measurements, or observations of binding of probes and analytes of this disclosure, the term “real-time” refers to measuring the status of a binding reaction while that reaction is occurring, either in the transient phase or in biochemical equilibrium. Real time measurements are performed contemporaneously with the monitored, measured, or observed binding events, as opposed to measurements taken after a reaction is fixed. Thus, a “real time” assay or measurement generally contains not only the measured and quantitated result, such as fluorescence, but expresses this at various time points, that is, in hours, minutes, seconds, milliseconds, nanoseconds, etc. “Real time” includes detection of the kinetic production of signal, comprising taking a plurality of readings in order to characterize the signal over a period of time. For example, a real time measurement can comprise the determination of the rate of increase or decrease in the amount of analyte bound to probe. While the measurement of signal in real-time can be useful for determining rate by measuring a change in the signal, in some cases the measurement of no change in signal can also be useful. For example, the lack of change of a signal over time can be an indication that hybridization has reached steady-state.

The measurements are performed in real time with a plurality of probes and analytes. The disclosure is useful for measuring probes and analytes that bind specifically to one another. A probe and an analyte pair that specifically bind to one another can be a specific binding pair.

The methods and systems of the disclosure can be used for measuring the binding of multiple specific binding pairs in the same solution at the same time. In one embodiment of the disclosure a plurality of probes which are members of a specific binding pair are attached to a surface, and this surface is used to measure the binding kinetics of a plurality of analytes which comprise the other member of the specific binding pair.

One aspect of the disclosure is a method of measuring binding between analyte and probe which lowers, and in some cases eliminates the noise which is present in conventional microarrays and which decreases the quality of the analyte-probe binding information. In conventional microarrays and most of the affinity-based biosensors, the detection and incubation phases of the assay procedure are carried out at different times. As shown in FIG. 1, conventional detection is carried out in a dry-phase at the point where a scanning and/or imaging technique used to assess the captured targets. This type of conventional microarray technique may not be amenable to the multiplex Q-PCR reactions of the present disclosure.

The following analysis illustrates inherent problems with conventional microarray analysis techniques, and the advantages of the real time microarray systems of the present disclosure in improving the quality of the binding measurement. Let x(t) denote the total number of captured analyte in a given spot of the microarray and/or affinity-based biosensor at a given time instant t. Furthermore, let x(t) denote the expected value of x(t) when the incubation process has reached biochemical equilibrium. A typical microarray procedure is focused on estimating x(t), and using its value as an indication of the analyte concentration in the sample; in fact, most data analysis techniques deduce their results based on x(t). Nevertheless, if we measure the number of captured analytes at time t₁ in the equilibrium, for any given microarray spot it holds that x(t₁)≠x(t). This is due to the inherent biochemical noise and other uncertainties of the system. This phenomenon is illustrated in FIG. 2, where the number of captured analytes in each spot of the microarray fluctuates in time, even in biochemical equilibrium. Accordingly, a single measurement taken at time t₁, which is what conventional microarray experiments provide, essentially samples a single point of the random process of analyte binding.

Now, consider the case where we are able measure x(t) multiple times, in real-time without the necessity of stopping the incubation and analyte binding reaction. This platform, which we call the real-time microarrays (RT-μArrays), has many advantages over the conventional method. In some embodiments of RT-μArrays, the kinetic of the bindings can be observed. Therefore, one can test whether the system has reached biochemical equilibrium or not. In other embodiments, multiple samples of x(t) are measured (see FIG. 3), and different averaging techniques and/or estimation algorithms can be used to estimate x(t) and other characteristics of process x(t).

FIG. 4 shows a block diagram of the errors associated with conventional DNA microarrays. These may be categorized into three stages: pre-hybridization (steps 1 and 2), hybridization (step 3), and post-hybridization (steps 4 and 5). The pre-hybridization errors arise from sample purification variations and the errors or variations in reverse transcribing mRNA to cDNA, in generating in vitro transcribed RNA complementary to the cDNA (cRNA, or IVT RNA), and or in labeling the analytes (step 1), and the errors arising from non-uniform probe spotting and or synthesis on the array (step 2). The hybridization errors arise from the inherent biochemical noise, cross-hybridization to similar targets, and the probe saturation (step 3). Post-hybridization errors include washing artifacts, image acquisition errors (step 4), and suboptimal detection (step 5). The most critical of these are probe density variations (step 2), probe saturation and cross-hybridization (step 3) and washing artifacts (step4).

The methods and systems of the present disclosure can compensate for all the above errors except for those of sample preparation (step 1). Probe density variations can be measured prior to incubation and therefore accounted for in post-processing (step 5), incubation noise can be reduced by taking many samples (rather than a single one), as mentioned earlier, probe saturation can be avoided by estimating target concentrations from the reaction rates, and finally washing is avoided altogether.

One aspect of the present disclosure is a method of measuring the binding of a plurality of analytes to a plurality of probes with a higher dynamic range than obtained with conventional microarrays. In some embodiments of the disclosure, the dynamic range is 3, 4, 5 or more orders of magnitude.

Methods

One aspect of the present disclosure is a method comprising measuring binding of analytes to probes on a microarray in real-time. In one embodiment, the method comprises the steps of: contacting a fluid volume comprising a plurality of different analytes with a solid substrate comprising a plurality of different probes, wherein the probes are capable of specifically binding with the analytes; and measuring signals at multiple time points while the fluid volume is in contact with the substrate, wherein the signals measured at multiple time points can be correlated with the amount of binding of the analytes with the probes. One embodiment of the method further comprises using the signals measured at multiple time points to determine the concentration of an analyte in the fluid volume.

In one embodiment the method involves the use of probe arrays in which each addressable location comprises a fluorescent moiety capable of emitting a signal that is quenchable upon binding of an analyte. For example, the quenchable moiety (e.g., a fluorescent moiety) is attached to the probe on the array or in close physical proximity thereto. The surface of such array will emit signal from each addressable location which can be detected using, for example, a series of lenses and a light detector (e.g., a CCD camera or CMOS image sensor). The analytes in the sample are tagged with a quencher moiety that can quench the signal from the quenchable moiety. When the quencher does not, itself, emit a light signal, there is little interference with the signal from the array. This diminishes the noise in the measurement of fluorescence from the array surface. During the course of a binding reaction between analytes and substrate-bound probes, the signal at each addressable location is quenched. The signal at each addressable location is measured in real time, for example, by a CCD camera focused on the array surface. As the signal at any location changes as a result of binding and quenching, the change is measured. These measurements over time allow determination of the kinetics of the reaction which, in turn, allows determination of the concentration of analytes in the sample.

Alternatively if the analytes can be labeled with a light-emitting reporter, such as a fluorescent label, and the background signal from these species can be diminished by focusing the detector at the array surface, thereby enhancing the signal from the surface bound moieties, and minimizing the noise from signal in solution. In addition, the interference from background fluorescence can be improved by having fluorescent labels on the surface with different emission spectra than the fluorescent moieties in solution on the analytes.

In another embodiment, the probes are attached to the surface of an array comprising sensors, such as a CMOS sensor array, which produce electrical signals that change as a result of binding events on the probes. This also affords real time measurement of a plurality of signals on an array (Hassibi and Lee, IEEE Sensors journal, 6-6, pp. 1380-1388, 2006, and Hassibi, A. “Integrated Microarrays,” Ph.D. Thesis Stanford University, 2005.

Accordingly, the methods of this disclosure allow real time measurements of a plurality of binding events on an array of probes on a solid support.

Analyte and Probe

One aspect of the present disclosure is the determination of the presence or amount of a nucleotide sequence. The term “nucleotide sequence” or “nucleic acid sequence” as used in this context refers to a sequence of nucleotides of which it is desired to know the presence or amount. The nucleotide sequence is typically RNA or DNA, or a sequence derived from RNA or DNA. Examples of nucleotide sequences are sequences corresponding to natural or synthetic RNA or DNA including genomic DNA and messenger RNA. The length of the sequence can be any length that can be amplified into amplicons, for example up to about 20, 50, 100, 200, 300, 400, 500, 600, 700, 800, 1,000, 1,200, 1,500, 2,000, 5,000, 10,000 or more than 10,000 nucleotides in length. It will be understood by those of skill in the art that as the number of nucleotides gets very large, the amplification can be less effective.

An “amplicon” as used herein is a molecular species that is created from the amplification of a nucleotide sequence. An amplicon is typically a polynucleotide such as RNA or DNA or mixtures thereof, in which the sequence of nucleotides in the amplicon correlates with the sequence of the nucleotide sequence from which it was generated (i.e. either corresponding to or complimentary to the sequence). The amplicon can be either single stranded or double stranded. In some embodiments, the amplicon is created using one or more primers that is incorporated into the amplicon. In some embodiments, the amplicon is generated in a polymerase chain reaction or PCR amplification, wherein two primers are used, creating what can be referred to as either a pair of complementary single stranded amplicons or a double-stranded amplicon.

The terms “probe” as used herein refers to a molecular species that binds to an analyte (such as an amplicon) in solution. A single probe or a single analyte is generally one chemical species. That is, a single analyte or probe may comprise many individual molecules. In some cases, a probe or analyte may be a set of molecules that are substantially identical. A “probe” can be any type of molecule that can specifically bind to an analyte in order to measure its amount in the fluid. A probe can be a molecule that can specifically hybridize to analytes in solution. The probes or analytes can be any type of chemical species. The probes or analytes are generally biomolecules such as nucleic acids, proteins, carbohydrates, lipids, or small molecules. The probe and analyte which bind to one another can each be the same or different types of species. The analyte or probe may be bound to another type of molecule and may comprise different molecules. For example, an analyte could be a protein carbohydrate complex, or a nucleic acid connected to protein. A probe-analyte pair can also be a receptor-ligand pair. Where the chemical species is large or made of multiple molecular components, the probe or analyte may be the portion of the molecule that is capable of binding, or may be the molecule as a whole. Examples of analytes that can be investigated by this disclosure include, but are not restricted to, agonists and antagonists for cell membrane receptors, toxins and venoms, viral epitopes, hormones (e.g., opiates, steroids, etc.), hormone receptors, peptides, enzymes, enzyme substrates, substrate analogs, transition state analogs, cofactors, drugs, proteins, antibodies, and hybridizing nucleic acids.

The probes of the present disclosure may be bound to the substrate or solid surface. For instance, the probe can comprise biological materials deposited so as to create spotted arrays; and materials synthesized, deposited, or positioned to form arrays according to other technologies. Thus, microarrays formed in accordance with any of these technologies may be referred to generally and collectively hereafter for convenience as “probe arrays.” Moreover, the term “probe” is not limited to probes immobilized in array format. Rather, the functions and methods described herein may also be employed with respect to other parallel assay devices. For example, these functions and methods may be applied with respect to probe-set identifiers that identify probes immobilized on or in beads, optical fibers, or other substrates or media. The construction of various probe arrays of the disclosure is described in more detail below.

In some embodiments, the probe and/or the analyte comprises a polynucleotide. The terms “polynucleotide,” “oligonucleotide,” “nucleic acid” and “nucleic acid molecule” as used herein include a polymeric form of nucleotides of any length, either ribonucleotides (RNA) or deoxyribonucleotides (DNA). This term refers only to the primary structure of the molecule. Thus, the term includes triple-, double- and single-stranded DNA, as well as triple-, double- and single-stranded RNA. It also includes modifications, such as by methylation and/or by capping, and unmodified forms of the polynucleotide. More particularly, the terms “polynucleotide,” “oligonucleotide,” “nucleic acid” and “nucleic acid molecule” include polydeoxyribonucleotides (containing 2-deoxy-D-ribose), polyribonucleotides (containing D-ribose), any other type of polynucleotide which is an N- or C-glycoside of a purine or pyrimidine base, and other polymers containing nonnucleotidic backbones. A nucleic acid of the present disclosure will generally contain phosphodiester bonds, although in some cases, as outlined below, nucleic acid analogs are included that may have alternate backbones, comprising, for example, phosphoramide (Beaucage et al., Tetrahedron 49(10):1925 (1993) and U.S. Pat. No. 5,644,048), phosphorodithioate (Briu et al., J. Am. Chem. Soc. 11 1:2321 (1989), O-methylphosphoroamidite linkages (see Eckstein, Oligonucleotides and Analogues: A Practical Approach, Oxford University Press), and peptide nucleic acid (PNA) backbones and linkages (see Carlsson et al., Nature 380:207 (1996)). Other analog nucleic acids include those with positive backbones (Denpcy et al., Proc. Natl. Acad. Sci. USA 92:6097 (1995); non-ionic backbones (U.S. Pat. Nos. 5,386,023, 5,637,684, 5,602,240, 5,216,141 and 4,469,863; Kiedrowshi et al., Angew. Chem. Intl. Ed. English 30:423 (1991); Letsinger et al., J. Am. Chem. Soc. 110:4470 (1988); Letsinger et al., Nucleoside & Nucleotide 13:1597 (1994); Chapters 2 and 3, ASC Symposium Series 580, “Carbohydrate Modifications in Antisense Research”, Ed. Y. S. Sanghui and P. Dan Cook; Mesmaeker et al., Bioorganic & Medicinal Chem. Lett. 4:395 (1994); Jeffs et al., J. Biomolecular NMR 34:17 (1994); Tetrahedron Lett. 37:743 (1996)) and non-ribose backbones, including those described in U.S. Pat. Nos. 5,235,033 and 5,034,506, and Chapters 6 and 7, ASC Symposium Series 580, “Carbohydrate Modifications in Antisense Research”, Ed. Y. S. Sanghui and P. Dan Cook. Nucleic acids containing one or more carbocyclic sugars are also included within the definition of nucleic acids (see Jenkins et al., Chem. Soc. Rev. (1995) pp 169-176). These modifications of the ribose-phosphate backbone may be done to facilitate the addition of labels, or to increase the stability and half-life of such molecules in physiological environments.

In some embodiments of the disclosure, oligonucleotides are used. An “oligonucleotide” as used herein is a single-stranded nucleic acid ranging in length from 2 to about 1000 nucleotides, more typically from 2 to about 500 nucleotides in length. In some embodiments, it is about 10 to about 100 nucleotides, and in some embodiments, about 20 to about 50 nucleotides. It can be advantageous to use an oligonucleotide in these size ranges as probes.

In some embodiments of the disclosure, for example, expression analysis, the disclosure is directed toward measuring the nucleic acid concentration in a sample. In some cases the nucleic acid concentration, or differences in nucleic acid concentration between different samples, reflects transcription levels or differences in transcription levels of a gene or genes. In these cases it can be desirable to provide a nucleic acid sample comprising mRNA transcript(s) of the gene or genes, or nucleic acids derived from the mRNA transcript(s). As used herein, a nucleic acid derived from an mRNA transcript refers to a nucleic acid for whose synthesis the mRNA transcript or a subsequence thereof has ultimately served as a template. Thus, a cDNA reverse transcribed from an mRNA, an RNA transcribed from that cDNA, a DNA amplified from the cDNA, an RNA transcribed from the amplified DNA, etc., are all derived from the mRNA transcript and detection of such derived products is indicative of the presence and/or abundance of the original transcript in a sample. Thus, suitable samples include, but are not limited to, mRNA transcripts of the gene or genes, cDNA reverse transcribed from the mRNA, cRNA transcribed from the cDNA, DNA amplified from the genes, RNA transcribed from amplified DNA, and the like. All of the above can comprise the nucleotide sequence for which the presence or amount is measured.

In some embodiments, where it is desired to quantify the transcription level (and thereby expression) of one or more genes in a sample, the nucleic acid sample is one in which the concentration of the mRNA transcript(s) of the gene or genes, or the concentration of the nucleic acids derived from the mRNA transcript(s), is proportional to the transcription level (and therefore expression level) of that gene. Similarly, it is preferred that the hybridization signal intensity be proportional to the amount of hybridized nucleic acid. While it is preferred that the proportionality be relatively strict (e.g., a doubling in transcription rate results in a doubling in mRNA transcript in the sample nucleic acid pool and a doubling in hybridization signal), one of skill will appreciate that the proportionality can be more relaxed and even non-linear. Thus, for example, an assay where a 5 fold difference in concentration of the target mRNA results in a 3 to 6 fold difference in hybridization intensity is sufficient for most purposes. Where more precise quantification is required appropriate controls can be run to correct for variations introduced in sample preparation and hybridization as described herein. In addition, serial dilutions of “standard” target mRNAs can be used to prepare calibration curves according to methods well known to those of skill in the art. Of course, where simple detection of the presence or absence of a transcript or large differences of changes in nucleic acid concentration are desired, no elaborate control or calibration is required.

In the simplest embodiment, such a nucleic acid sample is the total mRNA or a total cDNA isolated and/or otherwise derived from a biological sample. The term “biological sample”, as used herein, refers to a sample obtained from an organism or from components (e.g., cells) of an organism. The sample may be of any biological tissue or fluid. Frequently the sample will be a “clinical sample” which is a sample derived from a patient. Such samples include, but are not limited to, sputum, blood, blood cells (e.g., white cells), tissue or fine needle biopsy samples, urine, peritoneal fluid, and pleural fluid, or cells therefrom. Biological samples may also include sections of tissues such as frozen sections taken for histological purposes.

The nucleic acid (either genomic DNA or mRNA) may be isolated from the sample according to any of a number of methods well known to those of skill in the art. One of skill will appreciate that where alterations in the copy number of a gene are to be detected genomic DNA is preferably isolated. Conversely, where expression levels of a gene or genes are to be detected, preferably RNA (mRNA) is isolated.

Methods of isolating total mRNA are well known to those of skill in the art. For example, methods of isolation and purification of nucleic acids are described in detail in Chapter 3 of Laboratory Techniques in Biochemistry and Molecular Biology: Hybridization With Nucleic Acid Probes, Part I. Theory and Nucleic Acid Preparation, P. Tijssen, ed. Elsevier, N.Y. (1993) and Chapter 3 of Laboratory Techniques in Biochemistry and Molecular Biology: Hybridization With Nucleic Acid Probes, Part I. Theory and Nucleic Acid Preparation, P. Tijssen, ed. Elsevier, N.Y. (1993)).

Frequently, it is desirable to amplify the nucleic acid sample prior to hybridization. One of skill in the art will appreciate that whatever amplification method is used, if a quantitative result is desired, care must be taken to use a method that maintains or controls for the relative frequencies of the amplified nucleic acids.

In some embodiments, the probe and or the analyte may comprise a polypeptide. As used herein, the term “polypeptide” refers to a polymer of amino acids and does not refer to a specific length of the product; thus, peptides, oligopeptides, and proteins are included within the definition of polypeptide. This term also does not refer to or exclude post expression modifications of the polypeptide, for example, glycosylations, acetylations, phosphorylations and the like. The “peptide” refers to polypeptides of no more than about 50 amino acids, while term “protein” refers to longer polypeptides, typically with three-dimensional structures. Non-natural polypeptides containing one or more analogs of an amino acid (including, for example, unnatural amino acids, etc.), can also be useful in the disclosure, as can polypeptides with substituted linkages, as well as other modifications known in the art, both naturally occurring and non-naturally occurring. Polypeptides and proteins can have specific binding properties. For instance, an enzyme can have a region that binds specifically with a substrate, and/or has regions that bind to other proteins, such as the binding of enzyme subunits. Antibodies, which can have very specific binding properties, are also polypeptides.

In some embodiments the probe and/or analyte can comprise a carbohydrate such as a polysaccharide. The term polysaccharide, as used herein, refers to a carbohydrate which is a polyhydroxy aldehyde or ketone, or derivative thereof, having the empirical formula (CH₂O)_(n) wherein n is a whole integer, typically greater than 3. Monosaccharides, or simple sugars, consist of a single polyhydroxy aldehyde or ketone unit. Monosaccharides include, but are not limited to, ribose, 2-deoxy-ribose, glucose, mannose, xylose, galactose, fucose, fructose, etc. Disaccharides contain two monosaccharide units joined by a glycosidic linkage. Disaccharides include, for example, sucrose, lactose, maltose, cellobiose, and the like. Oligosaccharides typically contain from 2 to 10 monosaccharide units joined in glycosidic linkage. Polysaccharides (glycans) typically contain more than 10 such units and include, but are not limited to, molecules such as heparin, heparan sulfate, chondroitin sulfate, dermatan sulfate and polysaccharide derivatives thereof. The term “sugar” generally refers to mono-, di- or oligosaccharides. A saccharide may be substituted, for example, glucosamine, galactosamine, acetylglucose, acetylgalactose, N-acetylglucosamine, N-acetyl-galactosamine, galactosyl-N-acetylglucosamine, N-acetylneuraminic acid (sialic acid), etc. A saccharide may also reside as a component part of a larger molecule, for example, as the saccharide moiety of a nucleoside, a nucleotide, a polynucleotide, a DNA, an RNA, etc.

In some embodiments, the analyte and/or probe is a small molecule. Generally the small molecule will be an organic molecule, for example, biotin or digoxigenin, but in some cases, the analyte can be inorganic, for example an inorganic ion such as lithium, sodium, ferric, ferrous, etc. The small molecule can also be an organometallic compound, having both inorganic and organic components.

Probes on a Solid Substrate

For the methods of the present disclosure, the probes are attached to a solid substrate. The solid substrate may be biological, nonbiological, organic, inorganic, or a combination of any of these, existing as particles, strands, precipitates, gels, sheets, tubing, spheres, containers, capillaries, pads, slices, films, plates, slides, semiconductor integrated chips etc. The solid substrate is preferably flat but may take on alternative surface configurations. For example, the solid substrate may contain raised or depressed regions on which synthesis or deposition takes place. In some embodiments, the solid substrate will be chosen to provide appropriate light-absorbing characteristics. For example, the substrate may be a polymerized Langmuir Blodgett film, functionalized glass, Si, Ge, GaAs, GaP, SiO₂ SiN₄, modified silicon, or any one of a variety of gels or polymers such as (poly)tetrafluoroethylene, (poly)vinylidendifluoride, polystyrene, polycarbonate, or combinations thereof. The solid support and the chemistry used to attach the solid support are described in detail below.

The substrate can be a homogeneous solid and/or unmoving mass much larger than the capturing probe where the capturing probes are confined and/or immobilized within a certain distance of it. The mass of the substrate is generally at least 100 times larger than capturing probes mass. In certain embodiments, the surface of the substrate is planar with roughness of 0.1 nm to 100 nm, but typically between 1 nm to 10 nm. In other embodiments the substrate can be a porous surface with roughness of larger than 100 nm. In other embodiments, the surface of the substrate can be non-planar. Examples of non-planar substrates are spherical magnetic beads, spherical glass beads, and solid metal and/or semiconductor and/or dielectric particles.

For the methods of the present disclosure, the plurality of probes may be located in one addressable region and/or in multiple addressable regions on the solid substrate. In some embodiments the solid substrate has about 2, 3, 4, 5, 6, or 7-10, 10-50, 50-100, 100-500, 500-1,000, 1,000-5,000, 5,000-10,000, 10,000-50,000, 50,000-100,000, 100,000-500,000, 500,000-1,000,000 or over 1,000,000 addressable regions with probes.

In some embodiments it is also useful to have addressable regions which do not contain probe, for example, to act as control spots in order to increase the quality of the measurement, for example, by using binding to the spot to estimate and correct for non-specific binding.

Analyte/Probe Hybridization or Binding

The methods of the present disclosure utilize the measurement of the hybridization or binding characteristics of multiple analytes to multiple probes in real time. The method is particularly useful for characterizing the binding of probes and analytes which specifically bind or hybridize to one another. As used herein, a probe “specifically binds” to a specific analyte if it binds to that analyte with greater affinity than it binds to other substances in the sample.

The binding between the probes and the analytes in the present disclosure occurs in solution, usually in an aqueous solution. An aqueous solution is a solution comprising solvent and solute where the solvent is comprised mostly or completely of water. The methods of the disclosure, however, can be used in any type of solution where the binding between a probe and an analyte can occur and be observed.

Molecular recognition assays generally involve detecting binding events between two types of molecules. The strength of binding can be referred to as “affinity”. Affinities between biological molecules are influenced by non-covalent intermolecular interactions including, for example, hydrogen bonding, hydrophobic interactions, electrostatic interactions and Van der Waals forces. In multiplexed binding experiments, such as those contemplated here, a plurality of analytes and probes are involved. For example, the experiment may involve testing the binding between a pluralities of different nucleic acid molecules or between different proteins. In such experiments analytes preferentially will bind to probes for which they have the greater affinity. Thus, determining that a particular probe is involved in a binding event indicates the presence of an analyte in the sample that has sufficient affinity for the probe to meet the threshold level of detection of the detection system being used. One may be able to determine the identity of the binding partner based on the specificity and strength of binding between the probe and analyte.

The binding may be a receptor-ligand, enzyme-substrate, antibody-antigen, or a hybridization interaction. The probe/analyte binding pair or analyte/probe binding pair can be nucleic acid to nucleic acid, e.g. DNA/DNA, DNA/RNA, RNA/DNA, RNA/RNA, and RNA. The probe/analyte binding pair or analyte/probe binding pair can be a nucleic acid and a polypeptide, e.g. DNA/polypeptide and RNA/polypeptide, such as a sequence specific DNA binding protein. The probe/analyte binding pair or analyte/probe binding pair can be any nucleic acid and a small molecule, e.g. RNA/small molecule, DNA/small molecule. The probe/analyte binding pair or analyte/probe binding pair can be any nucleic acid and synthetic DNA/RNA binding ligands (such as polyamides) capable of sequence-specific DNA or RNA recognition. The probe/analyte binding pair or analyte/probe binding pair can be a protein and a small molecule or a small molecule and a protein, e.g. an enzyme or an antibody and a small molecule.

The probe/analyte binding pair or analyte/probe binding pair can be a carbohydrate and protein or a protein and a carbohydrate, a carbohydrate and a carbohydrate, a carbohydrate and a lipid, or lipid and a carbohydrate, a lipid and a protein, or a protein and a lipid, a lipid and a lipid.

The probe/analyte binding pair can comprise natural binding compounds such as natural enzymes and antibodies, and synthetic binding compounds. The probe/analyte binding can comprise aptamers, which are nucleic acid or polypeptide species that have been engineered to have specific binding properties, usually through repeated rounds of in vitro selection or equivalently, SELEX (systematic evolution of ligands by exponential enrichment).

The hybridization of the analyte to the probe may result in a change in signal. Generally, the signal due to hybridization may be proportional to the amount of hybridized analyte. While it can be advantageous to have the proportionality be relatively strict (e.g., a two fold change of the analyte amount and a two-fold change in hybridization signal), one of skill will appreciate that the proportionality can be more relaxed and even non-linear. Thus, for example, an assay where a 5 fold difference in concentration of the analyte may result in a 3 to 6 fold difference in hybridization intensity is sufficient for most purposes. Where more precise quantification is required appropriate controls can be run to correct for variations introduced in sample preparation and hybridization as described herein. Where simple detection of the presence or absence of a nucleotide sequence or large differences of changes in nucleic acid concentration are desired, no elaborate control or calibration is required.

Nucleic Acid Systems

One particularly useful aspect of the present disclosure involves specific hybridization between an analyte (e.g., an amplicon) and a probe, where both comprise nucleic acids.

As used herein an “oligonucleotide probe” is an oligonucleotide capable of binding to a target nucleic acid of complementary sequence through one or more types of chemical bonds, usually through complementary base pairing, usually through hydrogen bond formation. The oligonucleotide probe may include natural (i.e. A, G, C, or T) or modified bases (7-deazaguanosine, inosine, etc.). In addition, the bases in oligonucleotide probe may be joined by a linkage other than a phosphodiester bond, so long as it does not interfere with hybridization. Thus, oligonucleotide probes may be peptide nucleic acids in which the constituent bases are joined by peptide bonds rather than phosphodiester linkages. The oligonucleotide probes can also comprise locked nucleic acids (LNA), LNA, often referred to as inaccessible RNA, is a modified RNA nucleotide. The ribose moiety of the LNA nucleotide is modified with an extra bridge connecting 2′ and 4′ carbons. The bridge “locks” the ribose in 3′-endo structural conformation, which is often found in A-form of DNA or RNA. LNA nucleotides can be mixed with DNA or RNA bases in the oligonucleotide. Such oligomers are commercially available. The locked ribose conformation can enhance base stacking and backbone pre-organization, and can increase the thermal stability (melting temperature) of oligonucleotides.

The term “nucleic acid analyte” or “target nucleic acid” or “target” or “analyte” refers to a nucleic acid (often derived from a biological sample and hence referred to also as a sample nucleic acid), to which the oligonucleotide probe specifically hybridizes. It is recognized that the target nucleic acids can be derived from essentially any source of nucleic acids (e.g., including, but not limited to chemical syntheses, amplification reactions, forensic samples, etc.). It is either the presence or absence of one or more target nucleic acids that is to be detected, or the amount of one or more target nucleic acids that is to be quantified. The target nucleic acid(s) that are detected preferentially have nucleotide sequences that are complementary to the nucleic acid sequences of the corresponding probe(s) to which they specifically bind (hybridize). The term target nucleic acid may refer to the specific subsequence of a larger nucleic acid to which the probe specifically hybridizes, or to the overall sequence (e.g., gene or mRNA) whose abundance (concentration) and/or expression level it is desired to detect. The difference in usage will be apparent from context. In some cases, the term refers to amplicons of a nucleic acid.

In the present disclosure, the specific hybridization of an oligonucleotide probe to the target nucleic acid can be measured in real-time. An oligonucleotide probe will generally hybridize, bind, or duplex, with a particular nucleotide sequence under stringent conditions even when that sequence is present in a complex mixture. The term “stringent conditions” refers to conditions under which a probe will hybridize preferentially to its target subsequence, and to a lesser extent to, or not at all to, other sequences.

For nucleic acid systems, the oligonucleotide probes of the present disclosure are designed to be complementary to a nucleic acid target sequence, such that hybridization of the target sequence and the probes of the present disclosure occurs. This complementarity need not be perfect; there may be any number of base pair mismatches which will interfere with hybridization between the target sequence and the single stranded nucleic acids of the present disclosure. However, if the number of mutations is so great that no hybridization can occur under even the least stringent of hybridization conditions, the sequence is not a complementary target sequence. Thus, an oligonucleotide probe that is not substantially complementary to a nucleic acid analyte will not hybridize to it under normal reaction conditions.

The methods of the present disclosure thus can be used, for example, to determine the sequence identity of a nucleic acid analyte in solution by measuring the binding of the analyte with known probes. The sequence identity can be determined by comparing two optimally aligned sequences or subsequences over a comparison window or span, wherein the portion of the polynucleotide sequence in the comparison window may optionally comprise additions or deletions (i.e., gaps) as compared to the reference sequence (which does not comprise additions or deletions) for optimal alignment of the two sequences. The percentage is calculated by determining the number of positions at which the identical subunit (e.g. nucleic acid base or amino acid residue) occurs in both sequences to yield the number of matched positions, dividing the number of matched positions by the total number of positions in the window of comparison and multiplying the result by 100 to yield the percentage of sequence identity.

The methods of the current disclosure, when applied to nucleic acids, can be used for a variety of applications including, but not limited to, (1) mRNA or gene expression profiling, involving the monitoring of expression levels for example, for thousands of genes simultaneously. These results are relevant to many areas of biology and medicine, such as studying treatments, diseases, and developmental stages. For example, microarrays can be used to identify disease genes by comparing gene expression in diseased and normal cells; (2) comparative genomic hybridization (Array CGH), involving the assessment of large genomic rearrangements; (3) SNP detection arrays for identifying for Single Nucleotide Polymorphisms (SNP's) in the genome of populations; and chromatin immunoprecipitation (chIP) studies, which involve determining protein binding site occupancy throughout the genome, employing ChIP-on-chip technology.

The present disclosure can be very sensitive to differences in binding between analytes comprising different nucleic acid species, in some cases, allowing for the discrimination down to a single base pair mismatch. And because the present disclosure allows the simultaneous measurement of multiple binding events, it is possible to analyze several analytes simultaneously, where each is intentionally mismatched to different degrees. In order to do this, a “mismatch control” or “mismatch probe” which are probes whose sequence is deliberately selected not to be perfectly complementary to a particular target sequence can be used, for example in expression arrays. For each mismatch (MM) control in an array there, for example, exists a corresponding perfect match (PM) probe that is perfectly complementary to the same particular target sequence. In “generic” (e.g., random, arbitrary, haphazard, etc.) arrays, since the target nucleic acid(s) are unknown, perfect match and mismatch probes cannot be a priori determined, designed, or selected. In this instance, the probes can be provided as pairs where each pair of probes differs in one or more pre-selected nucleotides. Thus, while it is not known a priori which of the probes in the pair is the perfect match, it is known that when one probe specifically hybridizes to a particular target sequence, the other probe of the pair will act as a mismatch control for that target sequence. It will be appreciated that the perfect match and mismatch probes need not be provided as pairs, but may be provided as larger collections (e.g., 3, 4, 5, or more) of probes that differ from each other in particular preselected nucleotides. While the mismatch(s) may be located anywhere in the mismatch probe, terminal mismatches are less desirable as a terminal mismatch is less likely to prevent hybridization of the target sequence. In a particularly preferred embodiment, the mismatch is located at or near the center of the probe such that the mismatch is most likely to destabilize the duplex with the target sequence under the test hybridization conditions. In a particularly preferred embodiment, perfect matches differ from mismatch controls in a single centrally-located nucleotide.

It will be understood by one of skill in the art that control of the characteristics of the solution such as the stringency are important in using the present disclosure to measure the binding characteristics of a analyte-probe pair, or the concentration of an analyte (target nucleic acid). A variety of hybridization conditions may be used in the present disclosure, including high, moderate and low stringency conditions; see for example Maniatis et al., Molecular Cloning: A Laboratory Manual, 2d Edition, 1989, and Short Protocols in Molecular Biology, ed. Ausubel, et al, hereby incorporated by reference. Stringent conditions are sequence-dependent and will be different in different circumstances. Longer sequences hybridize specifically at higher temperatures. An extensive guide to the hybridization of nucleic acids is found in Tijssen, Techniques in Biochemistry and Molecular Biology—Hybridization with Nucleic Acid Probes, “Overview of principles of hybridization and the strategy of nucleic acid assays” (1993). In some embodiments, highly stringent conditions are used. In other embodiments, less stringent hybridization condition; for example, moderate or low stringency conditions may be used, as known in the art; see Maniatis and Ausubel, supra, and Tijssen, supra. The hybridization conditions may also vary when a non-ionic backbone, i.e. PNA is used, as is known in the art.

Stringent conditions are sequence-dependent and will be different in different circumstances. Longer sequences tend to hybridize specifically at higher temperatures. Generally, stringent conditions can be selected to be about 5.degree. C. lower than the thermal melting point (T_(m)) for the specific sequence at a defined ionic strength and pH. The T_(m) is the temperature (under defined ionic strength, pH, and nucleic acid concentration) at which 50% of the probes complementary to the target sequence hybridize to the target sequence at equilibrium. (As the target analyte sequences are generally present in excess, at T_(m), 50% of the probes are occupied at equilibrium). Typically, stringent conditions will be those in which the salt concentration is at least about 0.01 to 1.0 M Na ion concentration (or other salts) at pH 7.0 to 8.3 and the temperature is at least about 30° C. for short probes (e.g., 10 to 50 nucleotides). Stringent conditions may also be achieved with the addition of destabilizing agents such as formamide.

In some embodiments, the probe and or the analyte may comprise an antibody. As used herein, the term “antibody” refers to an immunoglobulin molecule or a fragment of an immunoglobulin molecule having the ability to specifically bind to a particular molecule, referred to as an antigen. The antibody may be an anti-receptor antibody specific for the receptor used in the assay. Thus, the antibody may be capable of specifically binding the receptor as the antigen. Antibodies and methods for their manufacture are well known in the art of immunology. The antibody may be produced, for example, by hybridoma cell lines, by immunization to elicit a polyclonal antibody response, or by recombinant host cells that have been transformed with a recombinant DNA expression vector that encodes the antibody. Antibodies include but are not limited to immunoglobulin molecules of any isotype (IgA, IgG, IgE, IgD, IgM), and active fragments including Fab, Fab′, F(ab′)₂, Facb, Fv, ScFv, Fd, V_(H) and V_(L). Antibodies include but are not limited to single chain antibodies, chimeric antibodies, mutants, fusion proteins, humanized antibodies and any other modified configuration of an immunoglobulin molecule that comprises an antigen recognition site of the required specificity.

The preparation of antibodies including antibody fragments and other modified forms is described, for example, in “Immunochemistry in Practice,” Johnstone and Thorpe, Eds., Blackwell Science, Cambridge, Mass., 1996; “Antibody Engineering,” 2.sup.nd edition, C. Borrebaeck, Ed., Oxford University Press, New York, 1995; “Immunoassay”, E. P. Diamandis and T. K. Christopoulos, Eds., Academic Press, Inc., San Diego, 1996; “Handbook of Experimental Immunology,” Herzenberg et al., Eds, Blackwell Science, Cambridge, Mass., 1996; and “Current Protocols in Molecular Biology” F. M. Ausubel et al., Eds., Greene Pub. Associates and Wiley Interscience, 1987, the disclosures of which are incorporated herein. A wide variety of antibodies also are available commercially.

In some embodiments, the probe and or the analyte may comprise two proteins. Protein-protein interactions can enable two or more proteins to associate. A large number of non-covalent bonds can form between the proteins when two protein surfaces are precisely matched, and these bonds account for the specificity of recognition. Protein-protein interactions are involved, for example, in the assembly of enzyme subunits; of multiprotein enzymatic complexes, or of molecular machines; in enzyme-substrate reactions; in antigen-antibody reactions; in forming the supramolecular structures of ribosomes, filaments, and viruses; in transport; and in the interaction of receptors on a cell with growth factors and hormones. Products of oncogenes can give rise to neoplastic transformation through protein-protein interactions. For example, some oncogenes encode protein kinases whose enzymatic activity on cellular target proteins leads to the cancerous state. Another example of a protein-protein interaction occurs when a virus infects a cell by recognizing a polypeptide receptor on the surface, and this interaction has been used to design antiviral agents. In some cases, protein-protein interactions can be dependent on protein modifications. For example, histone proteins can be modified at different positions with different chemical tags (e.g. phosphorylation, or methylation), and the modifications themselves be required or involved in the recognition by other proteins (e.g. chromatin remodeling and associated proteins).

Binding/Hybridization Kinetics

One aspect of the current disclosure is the use of the measurement of the binding kinetics to characterize binding of multiple probes and analytes (e.g., amplicons) in solution. The term “binding kinetics” or “hybridization kinetics” as used herein refers to the rate at which the binding of the analyte to the probe occurs in a binding or hybridization reaction. The term “binding reaction” as used herein describes the reaction between probes and analytes (e.g., amplicons). In some cases, binding reaction refers to the concurrent binding reactions of multiple analytes and probes, and in other cases, the term binding reaction refers to the reaction between a single probe with a single analyte. The meaning will be clear from the context of use. The kinetic measurements can be expressed as the amount of analyte bound to the probe as a function of time. The binding kinetics can provide information about the characteristics of the probe-analyte binding such as the strength of binding, the concentration of analyte, the competitive binding of an analyte, the density of the probes, or the existence and amount of cross-hybridization.

In order to determine binding kinetics, the signal at multiple time points must be determined. The signal at least two time points is required. In most cases, more than two time points will be desired in order to improve the quality of the kinetic information. In some embodiments the signal at, 2-10, 10-50, 50-100, 100-200, 200-400, 400-800, 800-1600, 1600-3200, 3200-6400, 6400-13000, or higher than 13,000 time points will be measured. One of ordinary skill in the art can determine the effective number of points for a given embodiment. For example, where few points are obtained, the quality of information about the binding event can be low, but where the number of data points is very high, the data quality may be high, but the handling, storage, and manipulation of the data can be cumbersome.

The frequency at which the signal is measured may depend on the kinetics of the binding reaction or reactions that are being monitored. As the frequency of measurements gets lower, the time between measurements gets longer. One way to characterize a binding reaction is to refer to the time at which half of the analyte will be bound (t_(1/2)). The binding reactions of the disclosure can have a (t_(1/2)) from on the order of milliseconds to on the order of hours, thus the frequency of measurements can vary by a wide range. The time between measurements will generally not be evenly spaced over the time of the binding reaction. In some embodiments, a short time between of measurements will be made at the onset of the reaction, and the time between measurements will be longer toward the end of the reaction. One advantage of the present disclosure is the ability to measure a wide range of binding rates. A high initial frequency of measurements allows the characterization of fast binding reactions which may have higher binding, and lower frequency of measurements allows the characterization of slower binding reactions. For example, points can initially be measured at a time between points on the order of a microsecond, then after about a millisecond, points can be measured at a time between points on the order of a millisecond, then after about a second, time points can be measured at a time between points on the order of a second. Any function can be used to ramp the change in measurement frequency with time. In some cases, as described below, changes in the reaction conditions, such as stringency or temperature changes will be made during a reaction, after which it may be desirable to change the frequency of measurements to measure the rates of reaction which will be changed by the change in reaction condition.

In some embodiments, a probe will have substantially no analyte bound to it at the beginning of the binding reaction, then the probe will be exposed to a solution containing the analyte, and the analyte will begin to bind, with more analyte bound to the probe with time. In some cases, the reaction will reach saturation, the point at which all of the analyte that is going to bind has bound. Generally, saturation will occur when a reaction has reached steady state. At steady state, in a given time period, just as many analytes are released as new analytes are bound (the on rate and off rate are equal). In some cases, with very strong binding, where the off-rate for the analyte is essentially zero, saturation will occur when substantially all of the analyte that can bind to the probe will have bound, has bound. Thus, while it is advantageous to measure a change in signal with time that can be correlated with binding kinetics, the measurement of a signal that does not change with time also provides information in the context of a real-time experiment, and can also be useful in the present disclosure. For example, in some cases the absence of a change in the signal will indicate the level of saturation. In other cases the absence of a change in signal can indicate that the rate of the reaction is very slow with respect to the change in time measured. It is thus a beneficial aspect of this disclosure to measure binding event in real time both where signals change with time and where the signals do not change with time.

One aspect of the methods of the present disclosure is the measurement of concentration of an analyte from the measurement of binding kinetics. Since analyte binding rate can be concentration-dependant, we can estimate the analyte abundance in the sample solution using binding rates.

In some embodiments, the concentration of analyte such as an amplicon can be determined by equations relating to the kinetics of the hybridization process. For example, suppose that the number of probes at a particular spot on the array prior to any hybridization is given by P₀. The probability of a specific target binding to the probe site is given by

Prob(binding)=k·Prob(target and probe in close proximity·Prob(probe is free),   (1)

where k≤1 depends of the bonds between the probe and the target and essentially a function of temperature, incubation conditions, and probe density. Here, the first probability is proportional to the number of target molecules available whereas the second probability is

$\begin{matrix} {{{{Probe}\left( {{probe}\mspace{14mu} {is}\mspace{14mu} {free}} \right)} = \frac{P(t)}{P_{0}}},} & (2) \end{matrix}$

where P(t) is the number of available probes at time t, i.e., those are not yet bound to any target. If we thus denote the forward and backwards target/probe binding reaction rates by K₊ and K⁻, respectively, we may write the following differential equation for the available probe concentration P(t):

$\begin{matrix} {\frac{{dP}(t)}{dt} = {{{- \frac{K_{+}}{P_{0}}}{P(t)}\left( {C - P_{0} - {P(t)}} \right)} + {K_{-}\left( {P_{0} - {P(t)}} \right)}}} & (3) \end{matrix}$

where C is the original target quantity in the solution so that C−(P₀−P(t)) represents the available target density at time t. The above is a Riccati differential equation that can be solved in closed form. However, instead of doing so, we can note that for small values of t we have P(t)≅P₀, so that the differential equation becomes

$\begin{matrix} {\frac{{dP}(t)}{dt} = {{- \frac{K_{+}}{P_{0}}}{P(t)}{C.}}} & (4) \end{matrix}$

This a first-order linear differential equation with time constant τ=P₀/K₊C. Accordingly, the target density can be determined from the reaction rate (or time constant) of P(t). In other words, using many sample measurements of P(t) at different times and fitting them to the curve

$\begin{matrix} {{P(t)} = {P_{0}{\exp \left( {{- \frac{K_{+}}{P_{0}}}C} \right)}t}} & (5) \end{matrix}$

allows us to estimate the target quantity C. In this case, the reaction rate (or inverse of the time constant) is proportional to the target concentration and inversely proportional to the probe density, something that has been observed in experiments.

One can also attempt to estimate C from the steady-state value of P(t), i.e., P_(∞). This can be found by setting dP(t)/dt=0 in the original Riccati equation which leads to a quadratic equation for P_(∞). In some simple cases, the solution to this quadratic equation can be considerably simplified.

When the target concentration is low: In this case, we can assume P₀>>C, so that we obtain

P ₂₈ =P ₀ −C,   (6)

i.e., the reduction in available probes is equal to the target concentration.

When the target concentration is high: In this case, we can assume that P₀<<C, so that we obtain

$\begin{matrix} {P_{\infty} = {\frac{K_{-}}{K_{+}} \cdot {\frac{P_{0}^{2}}{C}.}}} & (6) \end{matrix}$

In this case, the number of remaining probes is inversely proportional to the target concentration. This corresponds to probe saturation, which generally is not as good a method of determining C as determining C based on the reaction rate near the beginning of the reaction.

One aspect of the present disclosure is the determination of the binding of analyte to probe by measuring the rate near the beginning of the reaction. In addition to providing a more reliable estimate of C, measurement near the beginning of the reaction can shorten the time that is required to measure analyte binding over the time required for measuring binding from saturation. In some embodiments of the disclosure, the binding is measured during the time for less than about the first 0.1, 0.5, 1, 2, 3, 4, 5, 6, 8, 10, 12, 14, 18, 20, 25, 30, 40, 50, 60, 70, 80, or 90 percent of the analyte to bind as compared to the amount of analyte bound at saturation. In some embodiments, the binding kinetics are determined in a time for less than about the first 20% of the analyte to bind. In some embodiments, the binding kinetics are determined in a time for less than about the first 1-2% of the analyte to bind.

Changing Conditions During the Binding Experiment

One aspect of the methods of the present disclosure is a step of changing the conditions during the binding experiment. In conventional microarrays where only the end-point is determined, only a single set of binding conditions can be tested. In the methods of the present disclosure, the binding conditions can be changed in order to explore multiple sets of binding conditions during the same binding experiment. The condition which is changed can be, for example, any condition that affects the rate of binding of analyte to probe. The condition which is changed can be, for example, temperature, pH, stringency, analyte concentration, ionic strength, an electric field, or the addition of a competitive binding compound.

In some embodiments, the condition that is changed changes the rate of binding or hybridization. When measuring the binding of multiple analytes to probes in the same binding medium, as in the present disclosure, the kinetics of binding can vary widely for different analyte-probe combinations. The binding rate conditions can be varied, for example, by changing the temperature, concentration, ionic strength, pH, or by applying an electric potential. The binding rates for the different analytes can in some cases vary by many orders of magnitude, making it difficult and time consuming to measure the binding of all the analytes in one binding experiment. This ability to change the rate conditions can be used to improve the measurement of binding for multiple analytes that bind at different rates, for example by performing the initial part of the experiment under slower rate conditions, such that rapidly binding analytes can be readily measured, then raising the rate conditions such that more slowly binding analytes can be readily measured. This method of changing the binding rate during the binding experiment can also be used for better characterization of a single analyte or single set of analytes in solution, for instance, using binding rate conditions to measure the initial portion of the binding kinetics, then increasing the binding rate conditions to measure the later portion of the binding kinetics for a single analyte, for example, to establish the level of saturation. It will be understood by those of skill in the art that this method of changing the rate conditions can result in both improved quality of measurements, such as the measurement of analyte concentration, and/or in a savings of time. With the present method, for example by measuring the kinetics of binding, then changing the conditions to increase the rate of binding of weaker binding species, the time of the binding experiment can be reduced by greater than about 10%, 20%, 50%, 75%, or by a factor of 2, 4, 8, 10, 50, 100, 1000 or greater than 1000 over the times needed to obtain the same quality information using end-point binding methods.

In some embodiments, the condition that is changed is the stringency. As described above, the stringency can be changed by many factors including temperature, ionic strength, and the addition of compounds such as formamide. In some embodiments of the present disclosure, the medium is at one stringency at the beginning of the binding reaction, and at a later point the stringency of the medium is changed. This method can be used where different analytes or sets of analytes have different hybridization characteristics, for example, allowing the measurement of the binding of one set of analytes with a high stringency, then allowing the measurement of another set of analytes at a lower stringency in the same medium as part of the same binding experiment. This method can also be used for the characterization of binding for a single analyte by, for instance, measuring binding at high stringency at an initial portion of the binding reaction, then lowering the stringency and measuring a later portion of the binding reaction. The ability to change stringency can also be used to create conditions where a bound analyte becomes unbound, allowing, for instance, the measurement of the kinetics of binding at one stringency, followed by the measurement of release of the analyte into solution upon raising the stringency. This method also allows the binding of an analyte to a probe to be measured multiple times, for example, by measuring the kinetics of binding of the analyte under one set of stringency conditions, changing the stringency to release the analyte, for instance, by raising the stringency, then measuring the kinetics of binding of the analyte a subsequent time by changing the stringency conditions again, for example by lowering the stringency. Thus the ability to change the stringency during the binding reaction allows for the measurement of any number of binding and unbinding reactions with the same set of probes and analytes.

In some embodiments of the method of the present disclosure, an electric potential is applied during the binding reaction to the fluid volume to electrically change the stringency of the medium. In some embodiments, the system will provide an electrical stimulus to the capturing region using an electrode structure which is placed in proximity of the capturing region. If the analyte is an electro-active species and/or ion, the electrical stimulus can apply an electrostatic force of the analyte. In some embodiments the electrical potential is direct current (DC). In some embodiments, the electric potential is time-varying. In some embodiments the electric potential has both DC and time varying aspects. Their amplitude of the applied potential can be between 1 mV to 10V, but typically between 10 mV to 100 mV. The frequency of time-varying signal is between 1 Hz to 1000 MHz, but typically between 100 Hz to 100 kHz.

In some embodiments, the change in conditions is the addition of a competitive binding agent. For example, initially, a sample can be introduced which contains analyte that binds to a particular probe. The binding of that analyte can be monitored as described herein. Then, at any point during the binding of that analyte, an analyte that competes for the binding of that analyte to the probe can be added. The rate of displacement of the analyte by the competitive binding agent can then be measured, providing more information to characterize the binding of analyte to probe.

Detection of Signals

For the methods of the present disclosure, a signal is detected that can be correlated with the binding of analytes to the plurality of probes. The type of signals appropriate for the disclosure is any signal that can be amount of analyte bound to the plurality of probes. Appropriate signals include, for example, electrical, electrochemical, magnetic, mechanical, acoustic, or electromagnetic (light) signals. Examples of electrical signals useful in the present disclosure that can be correlated with analyte binding are capacitance and/or impedance. For example, analytes labeled with metals or metal clusters can change the capacitance and/or the impedance of a surface in contact with a fluid, allowing the amount of analyte bound to the probe on the surface to be determined. The electrical measurement can be made at any frequency including DC, 0-10 Hz, 10-100 Hz, 100-1000 Hz, 1 KHz-10 KHz, 10 KHz-100 KHz, 100 KHz-1 MHz, 1 MHz-10 MHZ, 10 MHz-100 MHz, 100 MHz-1 GHz, or above 1 GHz. In some embodiments, impedance spectroscopy can be used which obtains impedance versus frequency for any range of frequencies within the range of frequencies described above. Examples of electrochemical signals useful in the present disclosure that can be correlated with analyte binding include amperometric and voltammetric measurements, and/or measurements that involve the oxidation or reduction of redox species. For example, the analyte can be labeled with a compound which undergoes an oxidation or reduction reaction at a known redox potential, and the oxidative or reductive current can be correlated with the amount of analyte bound to surface probes. Examples of mechanical signals include the use of microelectromechanical (MEMS) devices. For example, the binding of analyte to probe on the surface of a small surface feature, such as a cantilever, can change the mass of the surface feature, the vibration frequency of which can then be correlated with the amount of analyte bound to the probe. Generally, the higher the mass, the lower the vibration frequency. Examples of acoustic signals include surface acoustic wave (SAW), and surface plasmon resonance signals. A surface acoustic wave (SAW) is an acoustic wave traveling along the surface of a material having some elasticity, with amplitude that typically decays exponentially with the depth of the substrate. The binding of labeled or unlabeled analyte to probe on a surface can change the SAW characteristics, e.g. amplitude, frequency in a manner that can be correlated with the amount of analyte bound to a probe. Surface plasmon resonance relies on surface plasmons, also known as surface plasmon polaritons, which are surface electromagnetic waves that propagate parallel, usually along a metal/dielectric interface. Since the wave is on the boundary of the metal and the external medium (water for example), these oscillations are very sensitive to any change of this boundary, such as the adsorption of molecules to the metal surface. The binding of labeled or unlabeled analyte to a probe attached to the surface can change the frequency of the resonant surface plasmon in a manner that can be correlated with the amount of analyte bound to the probes.

Particularly useful signals for the methods of the present disclosure are electromagnetic (light) signals. Examples of optical signals useful in the present disclosure are signals from fluorescence, luminescence, and absorption. As used herein, the terms “optical”, “electromagnetic” or “electromagnetic wave” and “light” are used interchangeably. Electromagnetic waves of any frequency and wavelength that can be correlated to the amount of analyte bound to probe on the surface can be used in the present disclosure including gamma rays, x-rays, ultraviolet radiation, visible radiation, infrared radiation, and microwaves. While some embodiments are described with reference to visible (optical) light, the descriptions are not meant to limit the embodiments to those particular electromagnetic frequencies.

For the methods of the present disclosure it is desired that the signal changes upon the binding of the analyte to the probe in a manner that correlates with the amount of analyte bound. In some cases, the change in signal will be a change in intensity of the signal. In some embodiments, the signal intensity will increase as more analyte is bound to probe. In some embodiments, the signal intensity will decrease as more analyte is bound to probe. In some embodiments, the change in signal is not a change in intensity, but can be any other change in the signal that can be correlated with analyte binding to probe. For example, the change in signal upon binding of the analyte/probe can be a change in the frequency of the signal. In some embodiments, the signal frequency will increase as more analyte is bound to probe. In some embodiments, the signal frequency will decrease as more analyte is bound to the probe.

The signal that is measured is generally the signal in the region of the solid surface. In some embodiments, signal from moieties attached to the surface is used as the signal that can be correlated with the amount of analyte bound to the probe. In some embodiments signal from the solution is used as the signal that can be correlated with the amount of analyte bound to the probe. The measurement of hybridization/binding of the analytes to the probes provides an analyte hybridization measurement. The analyte hybridization measurement can, in some cases, be correlated with the amount of analyte bound to the probe. As used herein, the concentration of a substance such as the analyte is the amount of the substance per volume of fluid in which the analyte is dissolved. Thus, a measurement of the concentration of the analyte may provide a measurement of the amount of the analyte when the volume of the fluid is known.

In some embodiments of the methods of the present disclosure, labels are attached to the analytes and/or the probes. Any label can be used on the analyte or probe which can be useful in the correlation of signal with the amount of analyte bound to the probe. It would be understood by those of skill in the art that the type of label with is used on the analyte and/or probe will depend on the type of signal which is being used, for example, as described above, a dense label for a mechanical signal, or a redox active label for a voltammetric measurement.

In some embodiments, the signal that can be correlated to the amount of analyte bound to probe is due to the buildup of label at the surface as more analyte is bound to the probes on the surface. For example, where the analyte has a fluorescent label, as more analyte binds, the intensity of the fluorescent signal can increase in a manner that can be correlated with the amount of analyte bound to probe on the surface. In some embodiments, the signal that can be correlated to the amount of analyte bound to probe is due to the release of label from the surface. For example, where the probe has a fluorescent label and the label is released into solution upon the binding of the analyte to the probe, the fluorescent intensity at the surface will decrease as more analyte is bound and more fluorescent label is released.

In some embodiments, the signal that can be correlated to the amount of analyte bound to probe is due to a change in the signal from label on the surface upon binding of the analyte to the probe. For example, where a fluorescent label is on the surface, and the analyte is labeled with a compound capable of changing the fluorescent signal of the surface fluorescent label upon binding of the analyte with the probe, the change in signal can be correlated with the amount of analyte bound to probe. In some embodiments, the analyte is labeled with a quencher, and the decrease in intensity from the surface fluorescent label due to quenching is correlated to the increased amount of analyte bound to probe. In some embodiments, the analyte is labeled with a fluorescent compound which can undergo energy transfer with the fluorescent label on the surface such that the increase in fluorescence from the analyte fluorescent label and/or the decrease in fluorescence from the surface fluorescent label can be correlated with the amount of analyte bound to probe. In some embodiments the surface fluorescent label is bound directly, e.g. covalently to the probe. In some embodiments, the surface fluorescent label is bound to the surface, is not bound to the probe, but is in sufficient proximity that the binding of the analyte to the probe produces a change in signal from the surface fluorescent label that can be correlated with the amount of analyte bound to probe.

In some embodiments, the analyte is unlabeled, and the binding characteristics and or concentration of the analyte is determined by competitive binding with another labeled species, which competes with the analyte for biding to a probe. For example, where we have a solution with an analyte, A, whose concentration we want to determine, and we have a competitive binding species, B, whose binding characteristics with probe and whose concentration are known, then using the present disclosure, we can use, for example, an array of probes on a surface to determine the concentration of A by determining the amount of competitive binding of B to a probe. For example, the probe is attached to a surface that is fluorescently labeled, and B is labeled with a quencher such that the level of quenching of the surface fluorescence can be correlated with the amount of B bound to the probe. The rate of binding of B to the probe is measured in real time, and the concentration of A is determined by knowing the characteristics of A as a competitive binder. In some embodiments, the amount of the competitive binding species does not need to be known beforehand. For instance, the kinetics of binding of B can be measured in the fluid volume, then the conditions can be changed, (e.g. increasing the stringency) such that B is released from the probe, then the analyte A is added, and the binding of B under competition with A is measured. This example illustrates an advantage of the being able to change the conditions of the medium during one experiment. In some cases, A and B can be the same species, where B is labeled, and the amount of B is known, and the amount of A can be determined by the kinetics of the binding of B. In some cases, A and B are not the same species, but compete for binding with a probe. This competitive binding real-time assay can be done with all types of molecular species described herein including nucleic acids, antibodies, enzymes, binding proteins, carbohydrates and lipids.

Electromagnetic Signals—Optical Methods

The use of optical detection provides a variety of useful ways of implementing the methods of the present disclosure. Optical methods include, without limitation, absorption, luminescence, and fluorescence.

Some embodiments of the disclosure involve measuring light absorption, for example by dyes. Dyes can absorb light within a given wavelength range allowing for the measurement of concentration of molecules that carry that dye. In the present disclosure, dyes can be used as labels, either on the analyte or on the probe. The amount of dye can be correlated with the amount of analyte bound to the surface in order to determine binding kinetics. Dyes can be, for example, small organic or organometallic compounds that can be, for example, covalently bound to the analyte to label the analyte. Dyes which absorb in the ultraviolet, visible, infrared, and which absorb outside these ranges can be used in the present disclosure. Methods such as attenuated total reflectance (ATR), for example for infrared, can be used to increase the sensitivity of the surface measurement.

Some embodiments of the disclosure involve measuring light generated by luminescence. Luminescence broadly includes chemiluminescence, bioluminescence, phosphorescence, and fluorescence. In some embodiments, chemiluminescence, wherein photons of light are created by a chemical reaction such as oxidation, can be used. Chemiluminescent species useful in the disclosure include, without limitation, luminol, cyalume, TMAE (tetrakis(dimethylamino)ethylene), oxalyl chloride, pyrogallol (1,2,3-trihydroxybenzene), lucigenin. In some embodiments, bioluminescence is used. Where the luminescence is bioluminescence, creation of the excited state derives from an enzyme catalyzed reaction. Bioluminescence derives from the capacity of living organisms to emit visible light through a variety of chemiluminescent reaction systems. Bioluminescence generally include three major components: a luciferin, a luciferase and molecular oxygen. However other components may also be required in some reactions, including cations (Ca⁺⁺ and Mg⁺⁺) and cofactors (ATP, NAD(P)H). Luciferases are enzymes that catalyze the oxidation of a substrate, luciferin, and produce an unstable intermediate. Light is emitted when the unstable intermediate decays to its ground state, generating oxyluciferin. Any of the different unrelated types of luciferin can be used herein including those from phyla which use a luciferin, known as coelenterazine, which contains a ring formed by three amino acids (2 tyrosines, and a phenylalanine). Photoproteins from animals such as jellyfish can be used where the “photoprotein” of the luciferin/luciferase system emits light upon calcium binding. Other bioluminescent systems as described in U.S. Patent Application 2007/0065818, and including bioluminescence resonance energy transfer (BRET) as described in U.S. Patent Application 2007/0077609 can be used in the present disclosure.

Fluorescent Systems

A useful embodiment of the present disclosure involves the use of fluorescence. As used herein, fluorescence refers to the process wherein a molecule relaxes to its ground state from an electronically excited state by emission of a photon. As used herein, the term fluorescence also encompasses phosphorescence. For fluorescence, a molecule is promoted to an electronically excited state by generally by the absorption of ultraviolet, visible, or near infrared radiation. The excited molecule then decays back to the ground state, or to a lower-lying excited electronic state, by emission of light. An advantage of fluorescence for the methods of the disclosure is its high sensitivity. Fluorimetry may achieve limits of detection several orders of magnitude lower than for absorption. Limits of detection of 10⁻¹⁰ M or lower are possible for intensely fluorescent molecules; in favorable cases under stringently controlled conditions, the ultimate limit of detection (a single molecule) may be reached.

A wide variety of fluorescent molecules can be utilized in the present disclosure including small molecules, fluorescent proteins and quantum dots. Useful fluorescent molecules (fluorophores) include, but are not limited to: 1,5 IAEDANS; 1,8-ANS; 4-Methylumbelliferone; 5-carboxy-2,7-dichlorofluorescein; 5-Carboxyfluorescein (5-FAM); 5-Carboxynapthofluorescein; 5-Carboxytetramethylrhodamine (5-TAMRA); 5-FAM (5-Carboxyfluorescein); 5-HAT (Hydroxy Tryptamine); 5-Hydroxy Tryptamine (HAT); 5-ROX (carboxy-X-rhodamine); 5-TAMRA (5-Carboxytetramethylrhodamine); 6-Carboxyrhodamine 6G; 6-CR 6G; 6-JOE; 7-Amino-4-methylcoumarin; 7-Aminoactinomycin D (7-AAD); 7-Hydroxy-4-methylcoumarin; 9-Amino-6-chloro-2-methoxyacridine; ABQ; Acid Fuchsin; ACMA (9-Amino-6-chloro-2-methoxyacridine); Acridine Orange; Acridine Red; Acridine Yellow; Acriflavin; Acriflavin Feulgen SITSA; Aequorin (Photoprotein); AFPs—AutoFluorescent Protein—(Quantum Biotechnologies); Alexa Fluor 350™; Alexa Fluor 430™; Alexa Fluor 488™; Alexa Fluor 532™; Alexa Fluor 546™; Alexa Fluor 568™; Alexa Fluor 594™; Alexa Fluor 633™; Alexa Fluor 647™; Alexa Fluor 660™; Alexa Fluor 680™; Alizarin Complexon; Alizarin Red; Allophycocyanin (APC); AMC, AMCA-S; AMCA (Aminomethylcoumarin); AMCA-X; Aminoactinomycin D; Aminocoumarin; Aminomethylcoumarin (AMCA); Anilin Blue; Anthrocyl stearate; APC (Allophycocyanin); APC-Cy7; APTRA-BTC; APTS; Astrazon Brilliant Red 4G; Astrazon Orange R; Astrazon Red 6B; Astrazon Yellow 7 GLL; Atabrine; ATTO-TAG™ CBQCA; ATTO-TAG™ FQ; Auramine; Aurophosphine G; Aurophosphine; BAO 9 (Bisaminophenyloxadiazole); BCECF (high pH); BCECF (low pH); Berberine Sulphate; Beta Lactamase; Bimane; Bisbenzamide; Bisbenzimide (Hoechst); bis-BTC; Blancophor FFG; Blancophor SV; BOBO™-1; BOBO™-3; Bodipy 492/515; Bodipy 493/503; Bodipy 500/510; Bodipy 505/515; Bodipy 530/550; Bodipy 542/563; Bodipy 558/568; Bodipy 564/570; Bodipy 576/589; Bodipy 581/591; Bodipy 630/650-X; Bodipy 650/665-X; Bodipy 665/676; Bodipy FI; Bodipy FL ATP; Bodipy FI-Ceramide; Bodipy R6G SE; Bodipy TMR; Bodipy TMR-X conjugate; Bodipy TMR-X, SE; Bodipy TR; Bodipy TR ATP; Bodipy TR-X SE; BO-PRO™-1; BO-PRO™-3; Brilliant Sulphoflavin FF; BTC; BTC-5N; Calcein; Calcein Blue; Calcium Crimson™; Calcium Green; Calcium Green-1 Ca.sup.2+ Dye; Calcium Green-2 Ca.sup.2+; Calcium Green-5N Ca.sup.2+; Calcium Green-C18 Ca.sup.2+; Calcium Orange; Calcofluor White; Carboxy-X-rhodamine (5-ROX); Cascade Blue™; Cascade Yellow; Catecholamine; CCF2 (GeneBlazer); CFDA; Chlorophyll; Chromomycin A; Chromomycin A; CL-NERF; CMFDA; Coumarin Phalloidin; C-phycocyanine; CPM Methylcoumarin; CTC; CTC Formazan; Cy2™; Cy3.1 8; Cy3.5™; Cy3™; Cy5.1 8; Cy5.5™; Cy5™; Cy7™; cyclic AMP Fluorosensor (FiCRhR); Dabcyl; Dansyl; Dansyl Amine; Dansyl Cadaverine; Dansyl Chloride; Dansyl DHPE; Dansyl fluoride; DAPI; Dapoxyl; Dapoxyl 2; Dapoxyl 3′ DCFDA; DCFH (Dichlorodihydrofluorescein Diacetate); DDAO; DHR (Dihydrorhodamine 123); Di-4-ANEPPS; Di-8-ANEPPS (non-ratio); DiA (4-Di-16-ASP); Dichlorodihydrofluorescein Diacetate (DCFH); DiD—Lipophilic Tracer; DiD (DiIC18(5)); DIDS; Dihydrorhodamine 123 (DHR); Dil (DiIC18(3)); Dinitrophenol; DiO (DiOC18(3)); DiR; DiR (DiIC18(7)); DM-NERF (high pH); DNP; Dopamine; DTAF; DY-630-NHS; DY-635-NHS; ELF 97; Eosin; Erythrosin; Erythrosin ITC; Ethidium Bromide; Ethidium homodimer-1 (EthD-1); Euchrysin; EukoLight; Europium (III) chloride; EYFP; Fast Blue; FDA; Feulgen (Pararosaniline); FIF (Formaldehyde Induced Fluorescence); FITC; Flazo Orange; Fluo-3; Fluo-4; Fluorescein (FITC); Fluorescein Diacetate; Fluoro-Emerald; Fluoro-Gold (Hydroxystilbamidine); Fluor-Ruby; FluorX; FM 1-43™; FM 4-46; Fura Red™ (high pH); Fura Red™/Fluo-3; Fura-2; Fura-2/BCECF; Genacryl Brilliant Red B; Genacryl Brilliant Yellow 10GF; Genacryl Pink 3G; Genacryl Yellow 5GF; GeneBlazer (CCF2); Gloxalic Acid; Granular blue; Haematoporphyrin; Hoechst 33258; Hoechst 33342; Hoechst 34580; HPTS; Hydroxycoumarin; Hydroxystilbamidine (FluoroGold); Hydroxytryptamine; Indo-1, high calcium; Indo-1, low calcium; Indodicarbocyanine (DiD); Indotricarbocyanine (DiR); Intrawhite Cf; JC-1; JO-JO-1; JO-PRO-1; LaserPro; Laurodan; LDS 751 (DNA); LDS 751 (RNA); Leucophor PAF; Leucophor SF; LeucophorWS; Lissamine Rhodamine; Lissamine Rhodamine B; Calcein/Ethidium homodimer; LOLO-1; LO-PRO-1; Lucifer Yellow; Lyso Tracker Blue; Lyso Tracker Blue-White; Lyso Tracker Green; Lyso Tracker Red; Lyso Tracker Yellow; LysoSensor Blue; LysoSensor Green; LysoSensor Yellow/Blue; Mag Green; Magdala Red (Phloxin B); Mag-Fura Red; Mag-Fura-2; Mag-Fura-5; Mag-Indo-1; Magnesium Green; Magnesium Orange; Malachite Green; Marina Blue; Maxilon Brilliant Flavin 10 GFF; Maxilon Brilliant Flavin 8 GFF; Merocyanin; Methoxycoumarin; Mitotracker Green FM; Mitotracker Orange; Mitotracker Red; Mitramycin; Monobromobimane; Monobromobimane (mBBr-GSH); Monochlorobimane; MPS (Methyl Green Pyronine Stilbene); NBD; NBD Amine; Nile Red; Nitrobenzoxadidole; Noradrenaline; Nuclear Fast Red; Nuclear Yellow; Nylosan Brilliant lavin E8G; Oregon Green; Oregon Green 488-X; Oregon Green™; Oregon Green™ 488; Oregon Green™ 500; Oregon Green™ 514; Pacific Blue; Pararosaniline (Feulgen); PBFI; PE-Cy5; PE-Cy7; PerCP; PerCP-Cy5.5; PE-TexasRed [Red 613]; Phloxin B (Magdala Red); Phorwite AR; Phorwite BKL; Phorwite Rev; Phorwite RPA; Phosphine 3R; PhotoResist; Phycoerythrin B [PE]; Phycoerythrin R [PE]; PKH26 (Sigma); PKH67; PMIA; Pontochrome Blue Black; POPO-1; POPO-3; PO-PRO-1; PO-PRO-3; Primuline; Procion Yellow; Propidium lodid (PL); PyMPO; Pyrene; Pyronine; Pyronine B; Pyrozal Brilliant Flavin 7GF; QSY 7; Quinacrine Mustard; Red 613 [PE-TexasRed]; Resorufin; RH 414; Rhod-2; Rhodamine; Rhodamine 110; Rhodamine 123; Rhodamine 5 GLD; Rhodamine 6G; Rhodamine B; Rhodamine B 200; Rhodamine B extra; Rhodamine BB; Rhodamine BG; Rhodamine Green; Rhodamine Phallicidine; Rhodamine Phalloidine; Rhodamine Red; Rhodamine WT; Rose Bengal; R-phycocyanine; R-phycoerythrin (PE); S65A; S65C; S65L; S65T; SBFI; Serotonin; Sevron Brilliant Red 2B; Sevron Brilliant Red 4G; Sevron Brilliant Red B; Sevron Orange; Sevron Yellow L; SITS; SITS (Primuline); SITS (Stilbene Isothiosulphonic Acid); SNAFL calcein; SNAFL-1; SNAFL-2; SNARF calcein; SNARF1; Sodium Green; SpectrumAqua; SpectrumGreen; SpectrumOrange; Spectrum Red; SPQ (6-methoxy-N-(3-sulfopropyl)quinolinium); Stilbene; Sulphorhodamine B can C; Sulphorhodamine Extra; SYTO 11; SYTO 12; SYTO 13; SYTO 14; SYTO 15; SYTO 16; SYTO 17; SYTO 18; SYTO 20; SYTO 21; SYTO 22; SYTO 23; SYTO 24; SYTO 25; SYTO 40; SYTO 41; SYTO 42; SYTO 43; SYTO 44; SYTO 45; SYTO 59; SYTO 60; SYTO 61; SYTO 62; SYTO 63; SYTO 64; SYTO 80; SYTO 81; SYTO 82; SYTO 83; SYTO 84; SYTO 85; SYTOX Blue; SYTOX Green; SYTOX Orange; Tetracycline; Tetramethylrhodamine (TRITC); Texas Red™; Texas Red-X™ conjugate; Thiadicarbocyanine (DiSC3); Thiazine Red R; Thiazole Orange; Thioflavin 5; Thioflavin S; Thioflavin TCN; Thiolyte; Thiozole Orange; Tinopol CBS (Calcofluor White); TMR; TO-PRO-1; TO-PRO-3; TO-PRO-5; TOTO-1; TOTO-3; TriColor (PE-Cy5); TRITC TetramethylRodaminelsoThioCyanate; True Blue; TruRed; Ultralite; Uranine B; Uvitex SFC; WW 781; X-Rhodamine; XRITC; Xylene Orange; Y66F; Y66H; Y66W; YO-PRO-1; YO-PRO-3; YOYO-1; YOYO-3, Sybr Green, Thiazole orange (interchelating dyes), or combinations thereof.

Some embodiments of the present disclosure include the Alexa Fluor dye series (from Molecular Probes/Invitrogen) which cover a broad spectrum and match the principal output wavelengths of common excitation sources such as Alexa Fluor 350, Alexa Fluor 405, 430, 488, 500, 514, 532, 546, 555, 568, 594, 610, 633, 635, 647, 660, 680, 700, and 750. Some embodiments of the present disclosure include the Cy Dye fluorophore series (GE Healthcare), also covering a wide spectrum such as Cy3, Cy3B, Cy3.5, Cy5, Cy5.5, Cy7. Some embodiments of the present disclosure include the Oyster dye fluorophores (Denovo Biolabels) such as Oyster-500, -550, -556, 645, 650, 656. Some embodiments of the present disclosure include the DY-Labels series (Dyomics), for example, with maxima of absorption that range from 418 nm (DY-415) to 844 nm (DY-831) such as DY-415, -495, -505, -547, -548, -549, -550, -554, -555, -556, -560, -590, -610, -615, -630, -631, -632, -633, -634, -635, -636, -647, -648, -649, -650, -651, -652, -675, -676, -677, -680, -681, -682, -700, -701, -730, -731, -732, -734, -750, -751, -752, -776, -780, -781, -782, -831, -480XL, -481XL, -485XL, -510XL, -520XL, -521XL. Some embodiments of the present disclosure include the ATTO fluorescent labels (ATTO-TEC GmbH) such as ATTO 390, 425, 465, 488, 495, 520, 532, 550, 565, 590, 594, 610, 611X, 620, 633, 635, 637, 647, 647N, 655, 680, 700, 725, 740. Some embodiments of the present disclosure include CAL Fluor and Quasar dyes (Biosearch Technologies) such as CAL Fluor Gold 540, CAL Fluor Orange 560, Quasar 570, CAL Fluor Red 590, CAL Fluor Red 610, CAL Fluor Red 635, Quasar 670. Some embodiments of the present disclosure include quantum dots such as the EviTags (Evident Technologies) or quantum dots of the Qdot series (Invitrogen) such as the Qdot 525, Qdot565, Qdot585, Qdot605, Qdot655, Qdot705, Qdot 800. Some embodiments of the present disclosure include fluorescein, rhodamine, and/or phycoerythrin.

FRET and Quenching

In some embodiments of the disclosure, fluorescence resonance energy transfer is used to produce a signal that can be correlated with the binding of the analyte to the probe. FRET arises from the properties of certain fluorophores. In FRET, energy is passed non-radiatively over a distance of about 1-10 nanometers between a donor molecule, which is a fluorophore, and an acceptor molecule. The donor absorbs a photon and transfers this energy non-radiatively to the acceptor (Forster, 1949, Z. Naturforsch. A4: 321-327; Clegg, 1992, Methods Enzymol. 211: 353-388). When two fluorophores whose excitation and emission spectra overlap are in close proximity, excitation of one fluorophore will cause it to emit light at wavelengths that are absorbed by and that stimulate the second fluorophore, causing it in turn to fluoresce. The excited-state energy of the first (donor) fluorophore is transferred by a resonance induced dipole-dipole interaction to the neighboring second (acceptor) fluorophore. As a result, the excited state lifetime of the donor molecule is decreased and its fluorescence is quenched, while the fluorescence intensity of the acceptor molecule is enhanced and depolarized. When the excited-state energy of the donor is transferred to a non-fluorophore acceptor, the fluorescence of the donor is quenched without subsequent emission of fluorescence by the acceptor. In this case, the acceptor functions as a quencher.

Pairs of molecules that can engage in fluorescence resonance energy transfer (FRET) are termed FRET pairs. In order for energy transfer to occur, the donor and acceptor molecules must typically be in close proximity (up to 7 to 10 nanometers. The efficiency of energy transfer can falls off rapidly with the distance between the donor and acceptor molecules.

Molecules that can be used in FRET include the fluorophores described above, and includes fluorescein, 5-carboxyfluorescein (FAM), 2′7′-dimethoxy-4′5′-dichloro-6-carboxyfluorescein (JOE), rhodamine, 6-carboxyrhodamine (R6G), N,N,N′,N′-tetramethyl-6-carboxyrhodamine (TAMRA), 6-carboxy-X-rhodamine (ROX), 4-(4′-dimethylaminophenylazo) benzoic acid (DABCYL), and 5-(2′-aminoethyl)aminonaphthalene-1-sulfonic acid (EDANS). Whether a fluorophore is a donor or an acceptor is defined by its excitation and emission spectra, and the fluorophore with which it is paired. For example, FAM is most efficiently excited by light with a wavelength of 488 nm, and emits light with a spectrum of 500 to 650 nm, and an emission maximum of 525 nm. FAM is a suitable donor fluorophore for use with JOE, TAMRA, and ROX (all of which have their excitation maximum at 514 nm).

In some embodiments of the methods of the present disclosure, the acceptor of the FRET pair is used to quench the fluorescence of the donor. In some cases, the acceptor has little to no fluorescence. The FRET acceptors that are useful for quenching are referred to as quenchers. Quenchers useful in the methods of the present disclosure include, without limitation, Black Hole Quencher Dyes (Biosearch Technologies such as BHQ-0, BHQ-1, BHQ-2, BHQ-3, BHQ-10; QSY Dye fluorescent quenchers (from Molecular Probes/Invitrogen) such as QSY7, QSY9, QSY21, QSY35, and other quenchers such as Dabcyl and Dabsyl; Cy5Q and Cy7Q and Dark Cyanine dyes (GE Healthcare), which can be used, for example, in conjunction with donor fluors such as Cy3B, Cy3, or Cy5; DY-Quenchers (Dyomics), such as DYQ-660 and DYQ-661; and ATTO fluorescent quenchers (ATTO-TEC GmbH), such as ATTO 540Q, 580Q, 612Q.

In some embodiments of the methods of the disclosure, both the analytes and the probes have labels that are members of a FRET pair, and the labels are attached such that when an analyte binds to a probe, FRET will occur between the labels, resulting in a change in signal that can be correlated with the binding of analyte to probe in real-time. The change in signal can be the decrease in the intensity of the donor and/or the increase in the intensity of the acceptor. The FRET pair can be chosen such that emission wavelength of the donor fluorophore is far enough from the emission wavelength of the acceptor fluorophore, that the signals can be independently measured. This allows the measurement of both the decrease in signal from the donor and the increase in signal from the acceptor at the same time, which can result in improvements in the quality of the measurement of binding. In some cases, the probe will have a label that is the donor of the donor-acceptor pair. In some cases, the analyte will have a label that is the donor of the donor acceptor pair.

In some embodiments of the methods of the disclosure, the analyte will have a fluorescent label that is a member of a FRET pair, and the other member of the FRET pair will be attached to the surface, wherein the member of the FRET pair attached to the surface is not covalently linked to the probe. In some cases, the analyte will have a label that is the donor of the donor-acceptor pair. In some cases, the analyte will have a label that is the acceptor of the donor acceptor pair. In some embodiments, the member of the FRET pair that is attached to the surface is attached to an oligonucleotide which is attached to the surface (a surface-bound label). The oligonucleotide that is labeled with the FRET pair can be a nucleotide sequence that does not have a sequence anticipated to specifically bind to an analyte. The use of a surface-bound label allows for the labeling of multiple areas of an array without having to label each specific binding probe. This can simplify the production of the array and reduce costs. We have found that even though the surface-bound FRET pairs are not covalently bound to the probe, they can be sensitive to the binding of the analyte labeled with the other member of the FRET pair in a manner that allows the change in signal to be correlated with the amount of analyte bound to probe.

In some embodiments of the methods of the present disclosure, the analyte is labeled with a quencher, and the probe is labeled with a donor fluorophore. The analyte is labeled with the quencher such that when analyte binds with the probe, the fluorescence from the fluorescent label on the probe is quenched. Thus, the signal, measured in real-time, can be correlated with the amount of binding of the analyte and the probe, allowing for the measurement of the kinetics of the binding. In some embodiments of the methods of the present disclosure, the analyte is labeled with a quencher, and the probe is labeled with a donor fluorophore, that is not covalently attached to it. The quencher is labeled such that when analyte binds with the probe, the fluorescence from the fluorescent label on the probe is quenched. Thus, the signal, measured in real-time, can be correlated with the amount of binding of the analyte and the probe, allowing for the measurement of the kinetics of the binding.

In some embodiments of the methods of the present disclosure, the analyte is labeled with a quencher, and the surface is labeled with a donor fluorophore wherein the donor fluorophore is not covalently linked to the probe (e.g. with a surface bound fluorescent label). The quencher is labeled such that when analyte binds with the probe, the fluorescence from the fluorescent label on the surface is quenched. Thus, the signal, measured in real-time, can be correlated with the amount of binding of the analyte and the probe, allowing for the measurement of the kinetics of the binding.

Where the probe is labeled with a fluorophore, one aspect of the disclosure is the use of an image of the fluorescently labeled probe on the surface obtained before binding has occurred in order to effectively establish a baseline signal for the state where no binding of analyte to probe has occurred. In conventional arrays, in which unlabeled probe is treated with labeled analyte, and the signal is measured after hybridization and washing, it can be difficult to know exactly how much probe is actually on the array in the region of interest. Thus, differences in array manufacture can affect the quality of the data. In the present disclosure, where the probe is labeled with fluorophore, the image of the labeled probe on the surface provides a measurement of the amount of probe actually on the surface, increasing the quality and reliability of the binding measurement.

One exemplary embodiment of the method of the disclosure is illustrated in FIGS. 5 and 6. FIG. 5B shows a top view of a 4 by 4 microarray that has 16 independently addressable spots, each spot having bound DNA probes, wherein the probes are labeled with fluorescent label. FIG. 5C shows a close up view of one of the spots illustrating the attached probe of sequence (A), each probe having a fluorescent label. FIG. 5D shows the close up view of a second spot with attached probes of sequence (B), each probe having a fluorescent label. FIG. 5A shows a side view of the array, showing that the array is in contact with the hybridization solution. FIG. 5 represents a time at which no analyte is bound to probe on the array.

FIG. 6 illustrates the same array as in FIG. 5 after hybridization for some time with target analytes (targets) having a quencher attached. FIGS. 6A and 6B shows a side view and top view of the array, still in contact with the hybridization solution. The different spots on the array in FIG. 6B have different light intensities, indicating that there is a different amount of binding of analyte at each spot, and therefore a different amount of fluorescence from the spots. FIG. 6C shows a close up view illustrating that a small amount of target (A) has specifically bound (hybridized) to probe (A) resulting in quenching of each molecule of probe to which analyte is bound. FIG. 6D illustrates that a larger amount of analyte (B) has specifically bound (hybridized) to probe (B), resulting in a higher level of quenching than observed for spot (A). The signal from each of the spots on the array can be measured at various time points during the binding reaction between analytes and probes, while the solution containing the analyte is in contact with the solid surface of the microarray, allowing a real-time measurement of the amount of analyte-probe binding, and allowing the measurement of binding kinetics at each spot.

The method of the present disclosure can be used to measure the presence or amount of nucleotide sequences in samples at low levels. In some embodiments, the presence or amount of nucleic acid can be measured where the nucleic acid is present in a sample at the level of nanomoles, picomoles, femtomoles. In some cases it can determine the presence or amount of nucleotide sequences down to a single molecule.

Nucleic Acid Amplification

One aspect of the present disclosure provides performing a nucleic acid amplification on two or more nucleotide sequences to produce two or more amplicons in a fluid that is in contact with an array of probes. The amplification of a nucleotide sequence can be performed by any method of amplification. Methods of amplification include, for example: polymerase chain reaction (PCR), strand displacement amplification (SDA), and nucleic acid sequence based amplification (NASBA), and Rolling Circle Amplification (RCA).

The polymerase chain reaction (PCR) is widely used and described, and involves the use of primer extension combined with thermal cycling to amplify a target sequence; see U.S. Pat. Nos. 4,683,195 and 4,683,202. In addition, there are a number of variations of PCR which also find use in the invention, including quantitative PCR or Q-PCR, “quantitative competitive PCR” or “QC-PCR”, “arbitrarily primed PCR” or “AP-PCR”, “immuno-PCR”, “Alu-PCR”, “PCR single strand conformational polymorphism” or “PCR-SSCP”, allelic PCR, “reverse transcriptase PCR” or “RT-PCR”, “biotin capture PCR”, “vectorette PCR”, “panhandle PCR”, and “PCR select cDNA subtraction”, among others. Strand displacement amplification (SDA) is generally described in Walker et al., in U.S. Pat. Nos. 5,455,166 and 5,130,238. Nucleic acid sequence based amplification (NASBA) is generally described in U.S. Pat. No. 5,409,818.

The amplification method can use temperature cycling or be isothermal. The amplification method can be exponential or linear. For amplifications with temperature cycling, a temperature cycle generally corresponds to an amplification cycle. Isothermal amplifications can in some cases have amplification cycles, such as denaturing cycles, and in other cases, the isothermal amplification reaction will occur monotonically with out any specific amplification cycle.

One aspect of the invention performing PCR amplification on two or more nucleotide sequences to produce two or more amplicons in a fluid that is in contact with an array of probes. PCR is used to amplify specific regions, or nucleotide sequences of a DNA strand. This region can be, for example, a single gene, just a part of a gene, or a non-coding sequence. PCR methods typically amplify DNA fragments of up to 10 kilo base pairs (kb), although some techniques allow for amplification of fragments up to 40 kb in size.

The PCR may include several components: (1) The DNA template that contains the region of the nucleic acid sequence to be amplified; (2) one or more primers, which are complementary to the DNA regions at the 5′ and 3′ ends of the DNA region that is to be amplified; (3) a DNA polymerase (e.g. Taq polymerase or another DNA polymerase with a temperature optimum at around 70° C.), used to synthesize a DNA copy of the region to be amplified; (4) Deoxynucleotide triphosphates, (dNTPs); (5) a buffer solution, which provides a suitable chemical environment for optimum activity and stability of the DNA polymerase; and (6) a divalent cation such as magnesium or manganese ions.

Prior to the first cycle, the reaction can be subjected to a hold step during an initialization step, the PCR reaction can be heated to a temperature of 94-98° C., and this temperature is then held for 1-9 minutes. This first hold is employed to ensure that most of the DNA template and primers are denatured, i.e., that the DNA is melted by disrupting the hydrogen bonds between complementary bases of the DNA strands. In some embodiments a hot-start PCR can be utilized.

Temperature cycling can then begin with one step at, for example, 94-98° C., for e.g. 20-30 seconds (denaturation step). The denaturation is followed by the annealing step. In this step the reaction temperature is lowered so that the primers can anneal to the single-stranded DNA template. The temperature at this step depends on the melting temperature of the primers, and is usually between 50-64° C., for e.g. 20-40 seconds.

The annealing step is followed by an extension/elongation step during which the DNA polymerase synthesizes new DNA strands complementary to the DNA template strands. The temperature at this step depends on the DNA polymerase used. Taq polymerase has a temperature optimum of about 70-74° C.; thus, a temperature of 72° C. may be used. The DNA polymerase condenses the 5′-phosphate group of the dNTPs with the 3′-hydroxyl group at the end of the nascent (extending) DNA strand, i.e., the polymerase adds dNTP's that are complementary to the template in 5′ to 3′ direction, thus reading the template in 3′ to 5′ direction. The extension time may depend on both on the DNA polymerase used and on the length of the DNA fragment to be amplified. Thus, in the process described, each temperature cycle has three phases; denaturation, annealing, and elongation. The amplified products from the amplification are referred to as amplicons. Generally, 10-40 cycles, usually 20-30 cycles of PCR are performed.

In some embodiments, the amplification methods of the invention utilize primers. A primer is a nucleic acid strand, or a related molecule that serves as a starting point for DNA replication. A primer is often required because most DNA polymerases cannot begin synthesizing a new DNA strand from scratch, but can only add to an existing strand of nucleotides. The primers of the invention are usually short, chemically synthesized DNA molecules with a length about 10 to about 30 bases. The length of primers can be for example about 20-30 nucleotides, and the sequence of the primers are complementary to the beginning and the end of the DNA fragment to be amplified. They anneal (adhere) to the DNA template at these starting and ending points, where DNA polymerase binds and begins the synthesis of the new DNA strand.

The design of primers is well known in the art. Pairs of primers should generally have the similar melting temperatures (T_(m)). A primer with a T_(m) significantly higher than the reaction's annealing temperature may mishybridize and extend at an incorrect location along the DNA sequence, while T_(m) significantly lower than the annealing temperature may fail to anneal and extend at all.

In some embodiments of the invention, degenerate primers are used. These are actually mixtures of similar, but not identical, primers. Degenerate primers can be used, for example, when primer design is based on protein sequence. As several different codons can code for one amino acid, it is often difficult to deduce which codon is used in a particular case. Therefore primer sequence corresponding to the amino acid isoleucine might be “ATH”, where A stands for adenine, T for thymine, and H for adenine, thymine, or cytosine, according to the genetic code for each codon. Use of degenerate primers can greatly reduce the specificity of the PCR amplification.

In some embodiments of the invention, the primers are labeled, and the labels become incorporated into the amplicons formed by such primers. The primers can be labeled with one or more labels that are for example fluorescent, quenchers, or members of a FRET pair. Methods of attaching these moieties to primers is well known in the art.

One aspect of the invention is an array of probes that is in fluid contact with an amplification reaction in which multiple amplicons are formed with multiple primer sets. The array of probes in fluid contact with the amplification reaction allows for the quantitation of the amount of amplicon generated at each cycle. As with Q-PCR, the amount of amplicon generated at each cycle can be plotted against the number of cycles, which can be used to accurately determine the amount of nucleic acid sequence from which the amplicons were generated.

The measurement of the amount of amplicon during or after each cycle is facilitated by measuring the hybridization kinetics of the amplicons to the probes on the array. In some embodiments, the rate of hybridization of the amplicon to the probe is measured during the annealing phase, the denaturing phase or the elongation phase. In a three phase PCR, typically, the rate of amplicon hybridization to probe is measured during the annealing phase of the PCR temperature cycle, where the rate of going from unbound to bound amplicon can be measured and the rate can be correlated with the concentration of the analytes in the fluid. Measuring binding during the denaturing phase can allow the determination of the “off’ rate the amplicons. In some embodiments, more than 3 temperature phases are used within a temperature cycle, and the separate temperature phases can be used do define specific hybridization conditions. For example, as shown in FIG. 25, a 5 phase temperature cycle can be used. The 5 phase temperature cycle shown in FIG. 25 has 3 phases that are similar to the 3 phases of a conventional PCR, and in addition, there is another denaturing phase followed by a hybridization phase. In this embodiment, the kinetics of amplicon hybridization is measured during the hybridization phase. The 5 phase method allows the hybridization phase to be optimized for measuring amplicon binding, while the annealing phase is optimized for primer annealing. In some embodiments, the temperature of the hybridization phase is lower than the temperature of the annealing phase. In some embodiments, the temperature of the hybridization phase is higher than that of the annealing phase.

In some embodiments, 3, 4, 5, 6 or more phases can be used. For example, in some embodiments, the hybridization phase can comprise multiple temperatures, allowing several hybridization conditions to be measured during one amplification cycle. In some cases, the number of phases can vary over the amplification, for example using a 3 phase cycle in some cycles, and a 5 phase cycle in others.

In some embodiments, amplicon hybridization is measured after every cycle. In some embodiments, amplicon hybridization is measured at some but not all of the amplification cycles. For example, in some embodiments, the first several cycles to about 10 cycles may provide little information because the level of amplicon is below the detection threshold, and in such cases, hybridization at few or none of the earlier cycles may be measured, while in the later cycles, hybridization at every cycle or almost every cycle may be measured. In contrast, the data during the exponential phase of amplification can yield the most useful data, and in this region, the amplicon hybridization may be measured during or after every or almost every cycle. In some embodiments, amplicon hybridization is measured on average during or after every 2, 3, 4, 5, 6, 7, 8, 9, or 10 amplification cycles.

One aspect of the invention is a method for performing multiplex quantitative PCR comprising (a) measuring the amount of 10 or more amplicons corresponding to 10 or more different nucleotide sequences in a single fluid volume during or after multiple amplification cycles to determine amplicon amount-amplification cycle values, and (b) using the amplicon amount-amplification cycle values to determine the presence or amount of the 10 or more nucleotide sequences in a sample. In some embodiments, the invention provides a method of performing multiplex PCR of 20 or more amplicons corresponding to 20 or more different nucleotide sequences are used to determine the amount of 20 or more nucleotide sequences. In some embodiments, the invention provides a method of performing multiplex PCR of 50 or more amplicons corresponding to 50 or more different nucleotide sequences are used to determine the amount of 50 or more nucleotide sequences. Multiplex Q-PCR refers to a quantitative PCR reaction wherein the concentration of more than one amplicon corresponding to more than one nucleic acid sequence is measured in the same amplification reaction in the same fluid volume. It is known in the art, for instance, that real-time PCR or Q-PCR systems can incorporate detector dyes with different emission wavelengths, such that each dye can be detected in the same solution. These conventional methods can be used for a small number of different amplicons, but are limited by the overlap of the fluorescent emission spectra. It is also known in the art, that where there are a larger number of amplicons, to split the sample into a number of different wells, for instance on a plate, and perform Q-PCR on the plate at one time in order to amplify the sample in each well of the plate. The present invention allows for larger numbers of amplicons, and therefore a larger number of nucleic acid sequences to be measured in the same amplification reaction in the same fluid. The present invention allows for example for a multiplex quantitative PCR reaction of greater that 10, 20, 50, 100, 200, 500, 1,000, 2,000, 5,000, 10,000, 50,000, 100,000, 500,000, 1,000,000 or more nucleic acid sequences in the same amplification reaction in the same fluid.

Measuring Cross-Hybridization

One aspect of the methods of the present disclosure is the step of performing an algorithm on real-time binding data to determine cross-hybridization for multiple probes on a substrate. One embodiment involves improving the quality of analyte-probe binding measurements by determining and correcting for cross-hybridization.

In its early stages, the probe-target binding kinetics can be described by a simple first-order differential equation whose time-domain solution is given by an exponential function; the rate of decay of the exponential function is determined by the binding reaction rate. Non-specific binding can have an adverse effect on the accuracy of microarray platforms, especially if the amount of the non-specific target is high relative to the specific target. One reason is that the specific and non-specific targets will compete for the same probe, and even though the probability of non-specific binding is much lower it may have an effect if the amount of the non-specific target is much higher. Fortunately, specific and non-specific bindings have different reaction rates, by virtue of the fact that the binding probabilities and target amounts are different; therefore, if both specific and non-specific (i.e., interfering) targets bind to a probe on a microarray or a parallel affinity-based biosensor, the signal measured by a RT-μArray system can be represented by a sum of exponentials,

μ(t)=Σα_(j) exp(β_(j) t),   (1)

where Σα_(j) gives the initial intensity of the probe spots, the β_(j) are the rates of decay for the specific (j=1) and non-specific (j=2, 3, . . . ) bindings, and where the α_(j) themselves depend on the reaction rates and target densities. In certain embodiments of the disclosure, we employ the so-called Prony method or one of its modifications. This method essentially represents the signal μ(t) in terms of the coefficients of the original differential equation. These coefficients are computed by finding eigenvalues of an appropriate covariance matrix. In other embodiments of the disclosure, algebraic characterization using singular value decomposition of the correlation matrix of the data is employed. In yet another embodiment of the disclosure, information-theoretic or Bayesian techniques can be used to detect a presence of the species that bind non-specifically, estimate the number of such species, and quantify their amounts.

The Basic Algorithm

The hybridization process in general satisfies a nonlinear differential equation. To see this, let p(t) denote the number of available probe molecules at a given spot at time t, and let n(t) denote the number of analytes in the solution that are specific to this spot. Thus, if the probability that an analyte be in close proximity to a probe molecule is P_(near), the probability that it binds to the probe once it is near in a unit interval of time is P_(h), and the probability that an analyte bound to a probe molecule is released in a unit interval of time is P_(r), then we may write

p(t+δ)−p(t)=δ(p ₀ −p(t))P _(r) −δp(t)n(t)P _(near) P _(h),   (1)

where p₀ denotes the initial number of probe molecules on this probe spot of the array. If we denote the total number of analyte molecules by N, then it is clear that n(t)=N−p₀+p(t). Letting δ→0, therefore gives

$\begin{matrix} {\frac{{dp}(t)}{dt} = {{\left( {p_{0} - {p(t)}} \right)P_{r}} - {{p(t)}\left( {N - p_{0} + {p(t)}} \right)P_{near}{P_{h}.}}}} & (2) \end{matrix}$

Upon rearranging terms, we have

$\begin{matrix} {{\frac{{dp}(t)}{dt} = {{p_{0}P_{r}} - {{p(t)}\left\lbrack {P_{r} + {\left( {N - p_{0}} \right)P_{near}P_{h}}} \right\rbrack} - {{p^{2}(t)}P_{near}P_{h}}}},} & (3) \end{matrix}$

which is the nonlinear equation we were seeking. This is a Riccati equation and can be solved in closed form (however, we shall not do so here). In any event, it is clear that by looking at the trajectory of p(t) one can glean information about the parameters N, p₀, P_(h), P_(r). For example, the steady-state of p(t), i.e., p₂₈ =p(∞), satisfies the quadratic equation

P _(near) P _(h) p _(∞) ²+[P _(r)+(N−p ₀)P _(near) P _(h)]p _(∞) −p ₀ P _(r)=0   (4)

and so measuring it, gives us information about the parameters of interest.

Determining the Analyte Concentration

The equations are often more instructive when written in terms of the number of probe molecules that have bound to analytes, i.e., q(t)=p₀−p(t). In this case we may write

$\begin{matrix} {{{- \frac{{dq}(t)}{dt}} = {{{q(t)}P_{r}} - {\left( {p_{0} - {q(t)}} \right)\left( {N - {q(t)}} \right)P_{near}P_{h}}}},} & (5) \end{matrix}$

-   -   which upon a rearrangement of terms becomes

$\begin{matrix} {\frac{{dq}(t)}{dt} = {{{Np}_{0}P_{near}P_{h}} - {\left\lbrack {P_{r} + {\left( {N + p_{0}} \right)P_{near}P_{h}}} \right\rbrack {q(t)}} + {P_{near}P_{h}{{q^{2}(t)}.}}}} & (6) \end{matrix}$

In the early phase of the hybridization process, i.e., when q(t) is very small, we may ignore the quadratic term in the differential equation and write

$\begin{matrix} {\frac{{dq}(t)}{dt} \approx {{{Np}_{0}P_{near}P_{h}} - {\left\lbrack {P_{r} + {\left( {N + p_{0}} \right)P_{near}P_{h}}} \right\rbrack {{q(t)}.}}}} & (7) \end{matrix}$

This has the solution

$\begin{matrix} {{q(t)} \approx {\frac{{Np}_{0}P_{near}P_{h}}{P_{r} + {\left( {N + p_{0}} \right)P_{near}P_{h}}}{\left( {1 - {\exp \left( {- {t\left\lbrack {P_{r} + {\left( {N + p_{0}} \right)P_{near}P_{h}}} \right\rbrack}} \right)}} \right).}}} & (8) \end{matrix}$

The above formula has several different ramifications; first the slope of increase of q(t), equivalently, the slope of decay of p(t), is given by

$\begin{matrix} {{\left. \frac{{dq}(t)}{dt} \right|_{t = 0} = {{Np}_{0}P_{near}P_{h}}},} & (9) \end{matrix}$

-   -   which is proportional to the number of analytes in the solution,         N.

Second, the reaction rate also has information on the number of analytes. In fact, the reaction rate is simply the coefficient of t in the exponential function for q(t), which is readily seen to be

reaction_rate=P _(r)+(N+p ₀)P _(near) P _(h).   (10)

Though this is not quite a linear relationship for N, it can still be used to estimate the number of analytes.

Of course, one can estimate N jointly from both the initial slope and the reaction rate. In particular, it is often true that P_(r) is very small and can be ignored compared to other terms. Therefore we shall take

reaction_rate=(N+p ₀)P _(near) P _(h)   (11)

Determining and Suppressing Cross-Hybridization

The other advantage of looking at the reaction rate is that it allows for one to deal with cross-hybridization and to suppress its effect. As mentioned earlier, in the early phase of the hybridization process, the number of available probe molecules, or equivalently the light intensity of a probe spot, decays exponentially with time. For example

C_(k) exp(−r_(k)t),   (12)

where C_(k) is a constant and r_(k) is the reaction rate that can be determined from the parameters of the experiment (probability of hybridization, number of analytes, number of probe molecules, etc.). In particular, as seen from (11), r_(k) is linear in the number of target analytes, N_(k), say.

If, in addition to hybridization of the target of interest, a number of other targets cross-hybridize to the same probe spot, the light intensity of the probe spot will decay as the sum of several exponentials, i.e.,

$\begin{matrix} {{{I(t)} = {\sum\limits_{k = 0}^{K - 1}{C_{k}{\exp \left( {{- r_{k}}t} \right)}}}},} & (13) \end{matrix}$

where k=0 corresponds to the desired target and k=1, . . . , K−1 corresponds to the K−1 cross-hybridizing analytes. The whole point is that the reaction rates for the different analytes differ (due to different numbers of analytes, binding probabilities, etc.) so that if we can estimate the reaction rates from (13), we should be able to determine the number of molecules for each different analyte.

The RT-uArray system samples the signal (i.e., the light intensity) of the probe spots at certain time intervals (multiples of Δ, say) and thus obtains the sequence

$\begin{matrix} {y_{n} = {{{I\left( {n\; \Delta} \right)} + {v\left( {n\; \Delta} \right)}} = {{\sum\limits_{k = 0}^{K - 1}{C_{k}{\exp \left( {{- n}\; \Delta \; r_{k}} \right)}}} + {v\left( {n\; \Delta} \right)}}}} & (14) \end{matrix}$

for n=0, 1, . . . T−1, where T is the total number of samples and v(t) represents the measurement noise. Defining u_(k)=exp(−Δr_(k)), we may write

$\begin{matrix} {y_{n} = {{\sum\limits_{k = 0}^{K - 1}{C_{k}u_{k}^{n}}} + {v_{n}.}}} & (15) \end{matrix}$

The goal is to (i) determine the value of K (i.e., how many analytes are binding to the probe spot), (ii) to estimate the values of the pairs {C_(k), u_(k)} for all k=1, . . . , K−1 and (iii) to determine the number of each analyte N_(k) (recall from (9) that C_(k) is proportional to the number of analytes and that from (11) the reaction rate is linear in N_(k)).

The problem of determining the number of exponential signals in noisy measurements, and estimating the individual rates, is a classical one in signal processing and is generally referred to as system identification. (There are a multitude of books and papers on this subject.) The basic idea is that, when y_(n) is the sum of K exponentials, it satisfies a K th order recurrence equation

y _(n) +h ₁ y _(n−1) + . . . +h _(K−1) y _(n−K+1) +h _(K) y _(n−K)=0.   (16)

Furthermore, the u_(k) are the roots of the polynomial

H(z)=z ^(K) +h ₁ z ^(Kn−1) + . . . +h _(K−1) z+h _(k).   (17)

In practice, since one observes a noisy signal, one first uses the measurements to form the so-called Hankel matrix

$\begin{matrix} \begin{pmatrix} y_{T/2} & y_{{T/2} - 1} & \ldots & y_{1} & y_{0} \\ y_{{T/2} + 1} & y_{T/2} & \ldots & y_{2} & y_{1} \\ \vdots & \vdots & \ddots & \vdots & \vdots \\ y_{T} & y_{T - 1} & \ldots & y_{{T/2} + 1} & y_{T/2} \end{pmatrix} & (18) \end{matrix}$

When y_(n) is the sum of K exponentials, the above Hankel matrix has rank K, i.e., only K nonzero eigenvalues. When y_(n) is noisy, the standard practice is to compute the singular values of the Hankel matrix and estimate K as being the number of significant singular values.

Once K has been determined, one forms the (T−K+1)×(K+1) Hankel matrix

$\begin{matrix} \begin{pmatrix} y_{K} & y_{K - 1} & \ldots & y_{1} & y_{0} \\ y_{K + 1} & y_{K} & \ldots & y_{2} & y_{1} \\ \vdots & \vdots & \ddots & \vdots & \vdots \\ y_{T} & y_{T - 1} & \ldots & y_{T - K + 1} & y_{T - K} \end{pmatrix} & (19) \end{matrix}$

-   -   and then identifies the vector (1 h₁ . . . h_(k))^(t) with the         smallest right singular vector of (19).

As mentioned earlier, the roots of H(z) are the desired u_(k), from which we determine the rates r_(k) and thereby the amounts of targets present. While the algorithm outlined above can be used, a variety of different techniques to find the u_(k), including, but not limited to, total least squares, ESPRIT, Prony's method, may be used.

In addition to the algorithm described above, other algorithmic solutions can be used, including the methods overviewed in (Petersson et al., Applied Mathematics and Computation, vol. 126, no. 1, February 2002, pp. 31-61). The methods described above provide the ability to quantify the amounts of the species that bind whether specifically or non-specifically.

Arrays

One aspect of the disclosure is an array that has a solid surface with a plurality of probes attached to it, where the array can be used for the real-time measurement of binding of analyte to the plurality of probes.

The arrays of the present disclosure comprise probes attached to a solid substrate. The solid substrate may be biological, nonbiological, organic, inorganic, or a combination of any of these, existing as particles, strands, precipitates, gels, sheets, tubing, spheres, containers, capillaries, pads, slices, films, plates, slides, semiconductor integrated chips, etc. The solid substrate is preferably flat but may take on alternative surface configurations. For example, the solid substrate may contain raised or depressed regions on which synthesis or deposition takes place. In some embodiments, the solid substrate will be chosen to provide appropriate light-absorbing characteristics. For example, the substrate may be a polymerized Langmuir Blodgett film, functionalized glass, Si, Ge, GaAs, GaP, SiO₂, SiN₄, modified silicon, or any one of a variety of gels or polymers such as (poly)tetrafluoroethylene, (poly)vinylidendifluoride, polystyrene, polycarbonate, or combinations thereof.

The substrate can be a homogeneous solid and/or unmoving mass much larger than the capturing probe where the capturing probes are confined and/or immobilized within a certain distance of it. The mass of the substrate is generally at least 100 times larger than capturing probes mass. In certain embodiments, the surface of the substrate is planar with roughness of 0.1 nm to 100 nm, but typically between 1 nm to 10 nm. In other embodiments the substrate can be a porous surface with roughness of larger than 100 nm. In other embodiments, the surface of the substrate can be non-planar. Examples of non-planar substrates are spherical magnetic beads, spherical glass beads, and solid metal and/or semiconductor and/or dielectric particles.

In some embodiments the substrate is optically clear, allowing light to be transmitted through the substrate, and allowing excitation and or detection to occur from light passing through the substrate. In some embodiments the substrate is opaque. In some embodiments, the substrate is reflective, allowing for light to pass through the surface layer containing probes and reflect back to a detector. In some embodiments, the array is incorporated into the fluid container in which the amplification reaction may take place. In some cases, the array is part of the wall or base of the container. In some cases the array mates with other elements, forming a seal, and creating a fluid container for carrying out the amplification reaction.

In some embodiments, glass slides are used to prepare biochips. The substrates (such as films or membranes) can also be made of silica, silicon, plastic, metal, metal-alloy, anopore, polymeric, and nylon. The surfaces of substrates can be treated with a layer of chemicals prior to attaching probes to enhance the binding or to inhibit non-specific binding during use. For example, glass slides can be coated with self-assembled monolayer (SAM) coatings, such as coatings of as aminoalkyl silanes, or of polymeric materials, such as acrylamide and proteins. A variety of commercially available slides can be used. Some examples of such slides include, but are not limited to, 3D-link® (Surmodics), EZ-Rays® (Mosaic Technologies), Fastslides® (Schleicher and Schuell), Superaldehyde®, and Superamine® (CEL Technologies).

Probes can be attached covalently to the solid surface of the substrate (but non-covalent attachment methods can also be used). In one embodiment, similar substrate, coating, and attachment chemistries are used for all three—UniScreen™, ProScreen™, NuScreen™—devices. In another embodiment, different chemistries are applied.

A number of different chemical surface modifiers can be added to substrates to attach the probes to the substrates. Examples of chemical surface modifiers include N-hydroxy succinimide (NHS) groups, amines, aldehydes, epoxides, carboxyl groups, hydroxyl groups, hydrazides, hydrophobic groups, membranes, maleimides, biotin, streptavidin, thiol groups, nickel chelates, photoreactive groups, boron groups, thioesters, cysteines, disulfide groups, alkyl and acyl halide groups, glutathiones, maltoses, azides, phosphates, and phosphines. Glass slides with such chemically modified surfaces are commercially available for a number of modifications. These can easily be prepared for the rest, using standard methods (Microarray Biochip Technologies, Mark Schena, Editor, March 2000, Biotechniques Books).

In one embodiment, substrate surfaces reactive towards amines are used. An advantage of this reaction is that it is fast, with no toxic by-products. Examples of such surfaces include NHS-esters, aldehyde, epoxide, acyl halide, and thio-ester. Most proteins, peptides, glycopeptides, etc. have free amine groups, which will react with such surfaces to link them covalently to these surfaces. Nucleic acid probes with internal or terminal amine groups can also be synthesized, and are commercially available (e.g., from IDT or Operon). Thus, nucleic acids can be bound (e.g., covalently or non-covalently) to surfaces using similar chemistries.

The substrate surfaces need not be reactive towards amines, but many substrate surfaces can be easily converted into amine-reactive substrates with coatings. Examples of coatings include amine coatings (which can be reacted with bis-NHS cross-linkers and other reagents), thiol coatings (which can be reacted with maleimide-NHS cross-linkers, etc.), gold coatings (which can be reacted with NHS-thiol cross linkers, etc.), streptavidin coatings (which can be reacted with bis-NHS cross-linkers, maleimide-NHS cross-linkers, biotin-NHS cross-linkers, etc.), and BSA coatings (which can be reacted with bis-NHS cross-linkers, maleimide-NHS cross-linkers, etc.). Alternatively, the probes, rather than the substrate, can be reacted with specific chemical modifiers to make them reactive to the respective surfaces.

A number of other multi-functional cross-linking agents can be used to convert the chemical reactivity of one kind of surface to another. These groups can be bifunctional, tri-functional, tetra-functional, and so on. They can also be homo-functional or hetero-functional. An example of a bi-functional cross-linker is X-Y-Z, where X and Z are two reactive groups, and Y is a connecting linker. Further, if X and Z are the same group, such as NHS-esters, the resulting cross-linker, NHS-Y-NHS, is a homo-bi-functional cross-linker and may connect an amine surface with an amine-group containing molecule. If X is NHS-ester and Z is a maleimide group, the resulting cross-linker, NHS-Y-maleimide, is a hetero-bi-functional cross-linker and may link an amine surface (or a thiol surface) with a thio-group (or amino-group) containing probe. Cross-linkers with a number of different functional groups are widely available. Examples of such functional groups include NHS-esters, thio-esters, alkyl halides, acyl halides (e.g., iodoacetamide), thiols, amines, cysteines, histidines, di-sulfides, maleimide, cis-diols, boronic acid, hydroxamic acid, azides, hydrazines, phosphines, photoreactive groups (e.g., anthraquinone, benzophenone), acrylamide (e.g., acrydite), affinity groups (e.g., biotin, streptavidin, maltose, maltose binding protein, glutathione, glutathione-S-transferase), aldehydes, ketones, carboxylic acids, phosphates, hydrophobic groups (e.g., phenyl, cholesterol), etc. Such cross-linkers can be reacted with the surface or with the probes or with both, in order to conjugate a probe to a surface.

Other alternatives include thiol reactive surfaces such as acrydite, maleimide, acyl halide and thio-ester surfaces. Such surfaces can covalently link proteins, peptides, glycopeptides, etc., via a (usually present) thiol group. Nucleic acid probes containing pendant thiol-groups can also be easily synthesized.

Alternatively, one can modify glass surfaces with molecules such as polyethylene glycol (PEG), e.g. PEGs of mixed lengths

Other surface modification alternatives (such as photo-crosslinkable surfaces and thermally cross-linkable surfaces) are known to those skilled in the art. Some technologies are commercially available, such as those from Mosiac Technologies (Waltham, Mass.), Exiqon™ (Vedbaek, Denmark), Schleicher and Schuell (Keene, N. H.), Surmodics™ (St. Paul, Minn.), Xenopore™ (Hawthorne, N.J.), Pamgene (Netherlands), Eppendorf (Germany), Prolinx (Bothell, Wash.), Spectral Genomics (Houston, Tex.), and Combimatrix™ (Bothell, Wash.).

Surfaces other than glass are also suitable for such devices. For example, metallic surfaces, such as gold, silicon, copper, titanium, and aluminum, metal oxides, such as silicon oxide, titanium oxide, and iron oxide, and plastics, such as polystyrene, and polyethylene, zeolites, and other materials can also be used. The devices can also be prepared on LED (Light Emitting Diode) and OLED (Organic Light Emitting Diode) surfaces. An array of LEDs or OLEDs can be used at the base of a probe array. An advantage of such systems is that they provide easy optoelectronic means of result readout. In some cases, the results can be read-out using a naked eye.

Probes can be deposited onto the substrates, e.g., onto a modified surface, using either contact-mode printing methods using solid pins, quill-pins, ink-jet systems, ring-and-pin systems, etc. (see, e.g., U.S. Pat. Nos. 6,083,763 and 6,110,426) or non-contact printing methods (using piezoelectric, bubble-jet, syringe, electro-kinetic, mechanical, or acoustic methods. Devices to deposit and distribute probes onto substrate surfaces are produced by, e.g., Packard Instruments. There are many other methods known in the art. Preferred devices for depositing, e.g., spotting, probes onto substrates include solid pins or quill pins (Telechem/Biorobotics).

The arrays of the present disclosure can also be three-dimensional arrays such as porous arrays. Such as devices consisting of one or more porous gel-bound probes in an array or an array of arrays format. A device can have one or more such structures and the structures can be of any geometric shape and form. The structures can also be vertically straight, angled, or twisted. Thus, each device denotes a (multiplexed) reaction site. The device can be used to perform reactions simultaneously or sequentially. Any of the known substrates and chemistries can be used to create such a device. For example, glass, silica, silicon wafers, plastic, metals; and metal alloys can all be used as the solid support (see. e.g., Stillman B A, Tonkinson J L, Schleicher and Schuell; Biotechniques, 29(3), 630-635, 2000; Rehmna et. al; Mosaic Technologies Inc., Nucleic Acids Research, 27(2), 649-655, 1999). In other embodiments, the intermediate species can be immobilized to the substrate using mechanical and/or electrostatic and/or and magnetic forces. Examples are magnetic beads with magnetic fields and glass beads with electrostatic fields. Bead based methods are described, for example in Gunderson et al., Genome Research, 870-877, 2004; Michael et al., Anal. Chem. 70, 1242-1248, 1998; Han et al., Nat. Biotechnol, 19, 631-635, 2001; and Lockhart et al., Nat. Biotechnol. 19, 1122-1123, 2001.

In other embodiments, the microarrays are manufactured through the in-situ synthesis of the probes. This in-situ synthesis can be achieved using phosphoramidite chemistry and/or combinatorial chemistry. In some cases, the deprotection steps are performed by photodeprotection (such as the Maskless Array Synthesizer (MAS) technology, (NimbleGen; or the photolithographic process, by Affymetrix). In other cases, deprotection can be achieved electrochemically (such as in the Combimatrix procedure). Microarrays for the present disclosure can also be manufactured by using the inkjet technology (Agilent).

For the arrays of the present disclosure, the plurality of probes may be located in one addressable region and/or in multiple addressable regions on the solid substrate. In some embodiments the solid substrate has about 2, 3, 4, 5, 6, or 7-10, 10-50, 50-100, 100-500, 500-1,000, 1,000-5,000, 5,000-10,000, 10,000-50,000, 50,000-100,000, 100,000-500,000, 500,000-1,000,000 or over 1,000,000 addressable regions with probes.

The spots may range in size from about 1 nm to 10 mm, in some embodiments from about 1 to 1000 micron and more in some embodiments from about 5 to 100 micron. The density of the spots may also vary, where the density is generally at in some embodiments about 1 spot/cm², in some embodiments at least about 100 spots/cm² and in other embodiments at least about 400 spots/cm², where the density may be as high as 10⁶ spots/cm² or higher.

The shape of the spots can be square, round, oval or any other arbitrary shape.

One aspect of the disclosure is an array that comprises a solid substrate having a surface and a plurality of different probes, wherein (a) the different probes are immobilized to the surface at different addressable locations, (b) the addressable locations comprise optical signal moieties bound to the surface, (c) the optical signal moieties are not bound directly to the probes, and (d) the optical signal from the optical signal moieties is capable of changing upon binding of an analyte to the probes. For these arrays, the optical signal moiety, for example, a fluorescent moiety is bound directly to the surface, but is not covalently bound to a probe, and in these cases the probe need not be labeled. The fluorescent moiety can be bound to the surface or synthesized in-situ by any of the methods described above for probes. The fluorescent moiety can be attached to an oligonucleotide that is not a probe, for example, having a sequence that is not complementary to target analytes such as amplicons in solution.

In one embodiment, a fluorescent moiety on the surface (surface-bound label) can be brought to the proximity of the probe via post-probe-synthesis or post-probe-deposition methods.

In some embodiments, the label can be bound to the probe by non-covalent means, such as by hybridization. For example, in certain embodiments of the present disclosure, some or all of the probes on the microarray may contain two different sequence segments: one segment that consists of a sequence that is specific to the probe and specific for the detection of a given target analyte such as an amplicon, and another segment that is a sequence that is common to all or many of the probes on the microarray. These two sequence segments can be immediately adjacent to each other on the probe, or separated by a linker. In this embodiment, the microarray is first hybridized with a (labeled oligonucleotide that is complementary to the common sequence segment, thus resulting in a microarray in which the spots or features where the probes are located also now contain fluorescent labels. These non-covalently bound labels can be bound to the probe such that FRET and or quenching of the label occurs upon binding of an analyte to the specific portion of the probe. This method can be advantageous, for instance by (1) lowering the cost of manufacturing microarrays that can be used in the real-time platform and/or (2) enabling the use of in-situ synthesized arrays in the real time platform. The labeled oligonucleotide can be a locked nucleic acid (LNA) oligonucleotide. LNA oligonucleotides can be useful because the LNA modification can result in enhanced hybridization properties (for example, diminishing the sequence length that is needed to achieve a certain Tm) (Jepsen et al., Oligonucleotides. 2004; 14(2):130-46).

Systems

One aspect of the disclosure is a system comprising: (a) a device with (i) a solid support having a surface and (ii) a plurality of different probes, wherein the different probes are immobilized to the surface; (b) a fluid volume comprising an analyte wherein the fluid volume is in contact with the solid support, and (c) a detector assembly comprising means to detect signals measured at multiple time points from each of a plurality of spots on the microarray while the fluid volume is in contact with the solid support.

The fluid volume can be introduced and held in the system by any method that will maintain the fluid in contact with the solid support. In many cases the fluid is held in a chamber. In some embodiments the chamber is open on one face, in other embodiments the chamber will mostly enclose the fluid. In some embodiments, the chamber will have one or more ports for introducing and/or removing material (usually fluids) from the chamber. In some embodiments one side of the chamber comprises the solid substrate on which the probes are attached. In some embodiments the chamber is integral to the solid substrate. In some embodiments, the chamber is a sub-assembly to which the solid substrate with probes can be removably attached. In some embodiments, some or all of the fluid chamber is an integral part of the instrument that comprises the detector. The chamber can be designed such that the signal that can be correlated with analyte-probe binding can be detected by a detector outside of the chamber. For instance, all or a portion of the chamber can be transparent to light to allow light in or out of the chamber to facilitate excitation and detection of fluorophores.

The system can incorporate one or more microfluidic devices. Microfluidic devices are fluid systems in which the volumes of fluid are small, typically on the order of microliters to nanoliters. In some embodiments the microfluidics can handle tens to thousands of samples in small volumes. Microfluidics used in the invention can be active or passive. By using active elements such as valves in the microfluidic device, microfluidic circuits can be created. This allows not only the use of small reagent volumes but also a high task parallelization since several procedures can be processed and physically be fitted on the same chip.

In microfluidic channels the flow of liquid can be completely laminar, that is, all of the fluid moves in the same direction and at the same speed. Unlike turbulent flow this may allow the transport of molecules in the fluid to be relatively predictable. The microfluidic devices can be made of glass or plastic. In some embodiments, polydimethylsiloxane (PDMS), a type of silicone can be used. Some advantages of PDMS are that it is inexpensive, optically clear and permeable to several substances, including gases. In some embodiments soft lithography or micromolding can be used to create PDMS based microfluidic devices. The devices can use pressure driven flow, electrodynamic flow, or wetting driven flow.

In some embodiments the microfluidic device has multiple chambers, each chamber having a real-time microarray. In some embodiments, the array is incorporated into the microfluidic device. In some embodiments, the microfluidic device is formed by adding features to a planar surface having multiple real-time microarrays in order to create chambers wherein the chamber correspond to the real-time microarray. In some embodiments, a substrate having three-dimensional features, for example a PDMS surface with wells and channels, is placed in contact with a surface having multiple real-time microarrays to form a microfluidic device having multiple arrays in multiple chambers.

A device having multiple chambers, each with a real-time microarray can be used in order to analyze multiple samples simultaneously. In some embodiments, multiple chambers have sample fluid derived from the same sample. Having sample fluid from the same sample in multiple chambers can be useful, for example to measure each with different arrays for analyzing different aspects of the same sample, or for example for increasing accuracy by parallel measurements on identical arrays. In some cases, different analytes within the same sample will have different optimum temperature profile conditions. Thus, in some embodiments, the same sample is divided into different fluid volumes, and the different fluid volumes are in different chambers with real-time microarrays; and at least some of the different fluid volumes are given a different temperature cycle.

In some embodiments, multiple chambers have sample fluid from different sources. Having sample fluid from different sources can be useful in order to increase throughput by measuring more samples in a given time period on a given instrument. In some embodiments, the microfluidic with multiple chambers containing real-time microarrays can be used for diagnostic applications. The device may have about 2, 3, 4, 5, 6, 7, 8, 9, 10, 10-15, 15-20, 20-30, 30-50, 50-75, 75-100, or more than 100 chambers each having a real time microarray.

The detector assembly can comprise a single detector or an array of detectors or transducers. As used herein, the terms detector and transducer are used interchangeably, and refer to a component that is capable of detecting a signal that can be correlated with the amount of analyte-probe binding. Where the detector system is an array of transducers, in some embodiments, the detector system is a fixed array of transducers, wherein one or more transducers in the transducer array corresponds to one independently addressable area of the array. In some embodiments, the detector or the array of transducers scans the array such that a given detector or transducer element detects signals from different addressable areas of the array during a binding reaction.

In some embodiments the detector array is in contact with the solid substrate. In some embodiments, the detector is at a distance away from the substrate. Where the detector is a distance away from the substrate, in some embodiments, the detector or detector array is capable of scanning the substrate in order to measure signal from multiple addressable areas. In some embodiments, the detector is an optical detector which is optically coupled to the substrate. The detector can be optically coupled to the substrate, for example with one or more lenses or waveguides.

FIG. 9 shows an example of a real-time microarray system where the detection system comprises a sensor array in intimate proximity of the capturing spots. In this embodiment, individual sensors detect the binding events of a single capturing spots.

In some embodiments, the detector is optically coupled through spatially confined excitation. This method is useful to optically couple the substrate to detector for a small region of substrate with probes. This method generally requires only a single detector, since only one region can create signal at a time. The method can be used in scanning systems, and is applicable in assays which an excitation is required for detection, such as fluorescence spectroscopy or surface plasmon resonance (SPR) methods.

In some embodiments, the detector is optically coupled through imaging using focal plane detector arrays: In this method the signal generated from the system is focused on a focal point detector array. This approach useful for optical detection systems where signal focusing can be carried out using lenses and other optical apparatus. Examples of detectors in these embodiments are complementary metal oxide semiconductor (CMOS) and charge coupled device (CCD) image sensors.

In some embodiments, the detector is optically coupled through surface imaging: In this method the detectors are placed in intimate proximity of the capturing probes such that the signal generated from the capturing region can only be observed by the dedicated detector. If a microarray with multiple capturing spots is used, multiple detectors are used, each dedicated to an individual spot. This method can be used in electrochemical-, optical-, and magnetic-based biosensors.

In some embodiments, the detector is optically coupled through surface imaging using signal couplers: In this method the detectors are not place in proximity of the capturing spots, however a signal coupler is used to direct signal from the capturing region to a detector. This method is generally used in optical detection systems where the signal coupling elements is a plurality of optical waveguide. Examples of signal coupling elements include fiber optic cables, fiber optic bundles, fiber optic faceplates, and light pipes.

The detectors of the present disclosure must be capable of capturing signal at multiple time points in real time, during the binding reaction. In some embodiments the detector is capable of measuring at least two signals in less than about 1 psec, 5 psec, 0.01 nsec, 0.05 nsec, 0.1 nsec, 0.5 nsec, 1 nsec, 5 nsec, 0.01 μsec, 0.05 μsec, 0.1 μsec, 0.5 μsec, 1 μsec, 5 μsec, 0.01 msec, 0.05 msec, 0.1 msec, 0.5 msec, 1 msec, 5 msec, 10 msec, 50 msec, 100 msec, 0.5 sec, 1 sec, 5 sec, 10 sec, or 60 sec.

In some embodiments the detector detects the signal at the substrate. In some embodiments the detector will detect the signal in the solution. In some embodiments, the detector will detect signal in both the solution and at the substrate.

In some embodiments the detector system is capable of detecting electrical, electrochemical, magnetic, mechanical, acoustic, or electromagnetic (light) signals.

Where the detector is capable of detecting optical signals, the detector can be, for example a photomultiplier tube (PMT), a CMOS sensor, or a (CCD) sensor. In some embodiments, the detector comprises a fiber-optic sensor.

In some embodiments, the system comprising the detector is capable of sensitive fluorescent measurements including synchronous fluorimetry, polarized fluorescent measurements, laser induced fluorescence, fluorescence decay, and time resolved fluorescence.

In some embodiments, the system comprises a light source, for example, for excitation of fluorescence. The light source is generally optically coupled to the substrate, for example with one or more lenses or waveguides. The light source can provide a single wavelength, e.g. a laser, or a band of wavelengths.

FIG. 7 shows a block diagram of the components of systems of the present disclosure. The system comprises of (i) reaction chamber which includes the microarray substrate, probes, analytes, and solution, (ii) heating and cooling modules and temperature sensor, (iii) temperature controller, and (iv) detector which is connected to an analysis block, where the latter is a part of a computing system.

FIG. 8 shows an example of a real-time microarray system where real-time binding of BHQ2 quencher-labeled cDNA molecules are detected using a fluorescent laser-scanning microscope. The substrate in this example is a transparent glass slides and the probes are 25 bp Cy5-labeled oligonucleotides. The light source (laser) and detector are both located on the back of the substrate.

In some embodiments, the system comprises an instrument that has a detector assembly, and a computing system, where the instrument can accept a sub-assembly. The sub assembly comprises a chamber that will hold the fluid volume and the solid substrate having a surface and a plurality of probes. The sub-assembly can be loaded into the instrument in order to monitor the hybridization of analytes to probes in real time.

In some embodiments, the system comprises: an assay assembly comprising means to engage a microarray and means to perform an assay on a surface of the microarray; and a detector assembly comprising means to detect signals measured at multiple time points from each of a plurality of spots on the microarray during the performance of the assay.

In some embodiments, the means to perform the assay comprise a compartment wherein the surface of the microarray comprises a floor of the compartment and means to deliver reagents and analytes into the compartment. Any method can be used to seal the microarray to the compartment including using adhesives and gaskets to seal the fluid. Any method can be used to deliver reagents and analytes including using syringes, pipettes, tubing, and capillaries.

In some embodiments, the system comprises a means of controlling the temperature. Control of temperature can be important to allow control of binding reaction rates, e.g. by controlling stringency. The temperature can be controlled by controlling the temperature at any place within the system including controlling the temperature of the fluid or the temperature of the solid substrate. Any means can be used for controlling the temperature including resistive heaters, Peltier devices, infrared heaters, fluid or gas flow. The temperatures can be the same or different for solution or substrate or different parts of each. Ideally the temperature is consistently controlled within the binding region. In some embodiments the temperature is controlled to within about 0.01, 0.05, 0.1, 0.5, or 1° C. In some embodiments, for example for a PCR amplification reaction, the temperature is controlled to within 0.1° C.

In some embodiments the system is capable of changing the temperature during the binding reaction or amplification in order to define the phases of the temperature cycles. In some embodiments, the temperature can be rapidly changed during the binding and/or amplification reaction. In some embodiments, the system is capable of changing the temperature at a rate of temperature change corresponding to a change of 1° C. in less than about 0.01 msec, 0.1 msec, 0.5 msec, 1 msec, 5 msec, 10 msec, 50 msec, 100 msec, 0.5 sec, 1 sec, 10 sec, or 60 sec. In some embodiments, for example for a PCR amplification reaction, the system is capable of changing temperature at a rate of greater than about 5° C., 10° C., or 20° C. per second.

In other embodiments the temperature is changed slowly, gradually ramping the temperature over the course of the binding reaction.

One embodiment of changing the temperature involves a change in temperature to change the binding stringency and probability. By changing temperature one can alter the stringency and observe the capturing the new capturing process with a new set of capturing probabilities.

In some embodiments, the system is capable of measuring temperature in one or multiple locations in the solution or on the solid substrate. The temperature can be measured by any methods including e.g., by thermometer, thermocouple, or thermochromic shift.

In some embodiments the system comprises a feedback loop for temperature control wherein the measured temperature is used as an input to the system in order to more accurately control temperature.

In some embodiments, the system comprises an apparatus to add or remove material from the fluid volume. In some embodiments, the system can add or remove a liquid from the fluid volume. In some embodiments, the system is capable of adding or removing material from the fluid volume in order to change the: concentration, pH, stringency, ionic strength, or to add or remove a competitive binding agent. In some embodiments, the system is capable of changing the volume of the fluid volume.

One embodiment of adding material to the fluid volume comprises the addition of incubation buffer. The incubation buffer may be the buffer in which the analytes are residing. By adding the incubation buffer, the concentration of analytes in the system will decrease and therefore the binding probability and kinetic of binding will both decrease. Furthermore, if the reaction has already reached equilibrium, the addition of the buffer will cause the system to move another equilibrium state in time.

Another embodiment of adding material to the fluid volume is adding a competing binding species. The competing species can be of the same nature of the analyte but in general they are molecules which have affinity to capturing probes. For DNA microarrays for example, the competing species can be synthesized DNA oligo-nucleotides with partially or completely complementary sequence to the capturing probes. In immunoassays, the competing species are antigens.

In some embodiments the system comprises elements to apply an electric potential to the fluid volume to electrically change the stringency of the medium. In some embodiments, the system will provide an electrical stimulus to the capturing region using an electrode structure which is placed in proximity of the capturing region. If the analyte is an electro-active species and/or ion, the electrical stimulus can apply an electrostatic force of the analyte. In certain embodiments, this electrostatic force is adjusted to apply force on the bonds between analyte and capturing probe. If the force is applied to detach the molecule, the affinity of the analyte-probe interaction is reduced and thus the stringency of the bond is evaluated. The electrical stimulus is generally a DC and/or time-varying electrical potentials. Their amplitude can be between 1 mV to 10V, but typically between 10 mV to 100 mV. The frequency of time-varying signal can be between 1 Hz to 1000 MHz, in some embodiments, the frequency of the time-varying signal is between 100 Hz to 100 kHz. The use of electric potential to control stringency is described in U.S. Pat. No. 6,048,690.

In some embodiments the system comprises a computing system for analyzing the detected signals. In some embodiments, the system is capable of transferring time point data sets to the computing system wherein each time point data set corresponds to detected signal at a time point, and the computing system is capable of analyzing the time point data sets, in order to determine a property related to the analyte and probe. The methods of the current disclosure can, in some cases, generate more data, sometimes significantly more data than for conventional microarrays. Thus a computer system and software that can store and manipulate the data (for instance, images taken at time points) can be essential components of the system. The data can be analyzed in real-time, as the reaction unfolds, or may be stored for later access.

The information corresponding to detected signal at each time point can be single values such as signal amplitude, or can be more complex information, for instance, where each set of signal information corresponds to an image of a region containing signal intensity values at multiple places within an addressable location.

The property related to analyte and/or probe can be, for example, analyte concentration, binding strength, or competitive binding, and cross-hybridization.

In some embodiments the computing system uses the algorithms described above for determining concentration and/or cross-hybridization.

One aspect of the present disclosure provides software for use in performing the calculation of the amount of nucleotide sequences in the sample from the information on the change in optical signal as a function of amplification cycle. The software may be capable of, for example, of calculating the CT value, including, for instance, fitting the exponential portion of the curve, determining the background threshold. The software is capable of carrying out these calculations efficiently for large numbers of amplicons and nucleotide sequences.

In some embodiments, the system has software for interfacing with the instrument, for example allowing the user to display information in real-time and allowing for user to interact with the reaction (i.e., add reagents, change the temperature, change the pH, dilution, etc.).

Also described herein are integrated biosensor arrays. One aspect of the present disclosure provides a fully integrated array which comprises a molecular recognition layer, and optical layer, and a sensor layer in a sandwich configuration. The biosensor array may be capable of measuring the presence, amount, and binding characteristics of multiple analytes in solution by measuring the binding of the analytes to probes in the molecular recognition layer which is on an open surface of the biosensor array. The molecular recognition layer may comprise a plurality of probes that are located on discrete, independently addressable regions. The optical layer may comprise an optical filter layer such as a multilayer dielectric which selectively allows light within a given wavelength range to pass through to the sensor array. The optical layer can also comprise an optical coupling layer, for example a fiber optic faceplate that guides the light from the molecular layer to the optical filter layer and/or the sensor array. The sensor layer comprises an array of sensors, wherein typically the sensors correspond to the independently addressable regions of probes.

The sensor array can be a semiconductor based photodiode array which can be created in a silicon substrate using, for example, a CMOS process. Where the diode array is made by conventional silicon processing such as CMOS, additional circuitry can be incorporated into the array to enhance the signal processing capability of the array and to improve data quality. The additional circuitry can be incorporated into each pixel of the array, for example comprising an in-pixel photocurrent detector, or can be placed on other portions of the silicon chip. In some cases, the sensor array has multiple sensors, for example, 10 to 1000 sensors which correspond to the same independently addressable region of probe. In some cases, different sensors that correspond to the same addressable region of probe correspond to different regions of wavelength (different colors). The biosensor array could have a few addressable regions, such as 3 to 20, or could have a large number of addressable regions from 1,000 to 100,000 or more.

The biosensor arrays can be incorporated into a system comprising a light source for illuminating the sample, a fluidic chamber for holding the fluid in contact with the molecular recognition layer, a temperature controller for controlling hybridization conditions, an interface for allowing electronic communication with the array. The system can in some cases measure multiple biosensor arrays simultaneously.

The biosensor arrays of the present disclosure can be used for the detection of the binding of analytes such as amplicons in real-time. By measuring real-time measurement of the kinetics of multiple binding events allows for an accurate and sensitive determination of binding characteristics or of analyte concentration for multiple species simultaneously. The abundance of target analytes in a sample can be evaluated by the real-time detection of target-probe binding events. In some embodiments, real-time microarray (RT-μArray) detection systems measure the concentration of the target analytes by analyzing the binding rates and/or the equilibrium concentration of the captured analytes in a single and/or plurality of spots. The measurement of analyte concentration during binding can avoid errors introduced in the washing and drying process used in many conventional microarrays. Measuring during binding also has the advantage of taking less time than waiting for saturation of binding before measuring analyte binding.

The molecular recognition layer can comprise fluorescent entities that are attached to the surface that are quenched by analytes comprising quenchers in solution. This method can be advantageous for measuring binding in the presence of solution because the analytes comprising quenchers can be designed so as to contribute minimally to background fluorescence. The fluorescent entities can be bound directly to the probe or can be bound to the surface in the vicinity of the probe.

The integrated biosensor arrays of the disclosure can be used to measure the concentration or binding characteristics of many types of probe-analyte binding pairs including proteins and nucleic acids. The measurement of nucleic acid hybridization on the biosensor arrays of the disclosure can be used to perform genomic and genetic expression analysis accurately and rapidly on many nucleotide sequences simultaneously. The biosensor arrays of the present disclosure can be used for accurate diagnostic and medical testing.

Biosensor Array

The biosensor array (bioarray) of the present disclosure is an integrated array comprising a molecular recognition layer, an optical layer, and a sensor layer.

A technique to measure the amount of captured analytes in microarrays (i.e., transduction method) is based on fluorescence spectroscopy. Previous microarray technology and biosensors have often been focused on systems with electrochemical transducers or partially integrated fluorescent and bioluminescence detectors. An example of a conventional microarray is shown in FIG. 26. The system may consist of an affinity-based assay located in contact with an array containing independently addressable probe locations. After a step of incubation to allow an analytes in the affinity-based assay to bind with an appropriate probe, the binding affinity can be detected by a sensor. Many convention systems may be two step systems as illustrated in FIG. 26.

In some embodiments, the devices, systems, and methods of the disclosure utilize fluorescent detection. An example of a microarray technology based upon fluorescent detection is illustrated in FIG. 27. A microarray on a glass slide may contain independently addressable locations containing capturing probes, as illustrated. A fluorescent label may be attached to a target analyte. An incubation step may be carried out to allow the target analyte to bind to the capturing probe. After the incubation step is complete, a fluorescent image can be taken of the microarray and the different independently addressable locations emit different signals corresponding to the amount of analyte bound on the location. In the present disclosure, the optical sensors may be integrated into the substrate onto which capturing probes are bound.

An aspect of the present disclosure provides a fully integrated biosensor array comprising e.g., in order, a molecular recognition layer, an optical layer and a sensor layer integrated in a sandwich configuration. The molecular recognition layer comprises an open surface and a plurality of different probes attached at different independently addressable locations to the open surface. The molecular recognition layer can also transmit light to the optical layer. The optical layer comprises an optical filter layer, wherein the optical layer transmits light from the molecular recognition layer to the sensor layer. The transmittal of light between layers can be filtered by the optical layer. The sensor layer comprises an array of optical sensors that detects the filtered light transmitted through the optical layer.

An integrated biosensor array of the disclosure can measure binding of analytes in real-time. FIG. 9 illustrates an embodiment of a device of the disclosure. An integrated biosensor microarray that can detect binding kinetics of an assay is in contact with an affinity-based assay. The biosensor array comprises a molecular recognition layer comprising binding probes in optical communication a sensor for detecting binding to the probes in real-time.

An integrated fluorescent-based microarray system for real-time measurement of the binding of analyte to a plurality of probes that includes the capturing probe layer, fluorescent emission filter, and image sensor can be built using a standard complementary metal-oxide semiconductor (CMOS) process.

The devices of the disclosure can measure binding of analytes to a plurality of probes on surface in “real-time”. As used herein in reference to monitoring, measurements, or observations of binding of probes and analytes of this disclosure, the term “real-time” refers to measuring the status of a binding reaction while that reaction is occurring, either in the transient phase or in biochemical equilibrium. Real-time measurements are performed contemporaneously with the monitored, measured, or observed binding events, as opposed to measurements taken after a reaction. Thus, a “real-time” assay or measurement contains not only the measured and quantities result, such as fluorescence, but expresses this at various time points, that is, in hours, minutes, seconds, milliseconds, nanoseconds, etc. “Real-time” includes detection of the kinetic production of signal, comprising taking a plurality of readings in order to characterize the signal over a period of time. For example, a real-time measurement can comprise the determination of the rate of increase or decrease in the amount of analyte bound to probe.

Real-time measurement can include the measurement of the binding kinetics to characterize binding of multiple probes and analytes in solution. In some cases, binding reaction refers to the concurrent binding reactions of multiple analytes and probes, and in other cases, the term binding reaction refers to the reaction between a single probe with a single analyte. The meaning will be clear from the context of use. The kinetic measurements can be expressed as the amount of analyte bound to the probe as a function of time. The binding kinetics can provide information about the characteristics of the probe-analyte binding such as the strength of binding, the concentration of analyte, the competitive binding of an analyte, the density of the probes, or the existence and amount of cross-hybridization.

In order to determine binding kinetics, the signal at multiple time points must be determined. The signal at least two time points is required. In most cases, more than two time points will be desired in order to improve the quality of the kinetic information. In some embodiments the signal at, 2-10, 10-50, 50-100, 100-200, 200-400, 400-800, 800-1600, 1600-3200, 3200-6400, 6400-13000, or higher than 13,000 time points will be measured. One of ordinary skill in the art can determine the effective number of points for a given embodiment.

The frequency at which the signal is measured will depend on the kinetics of the binding reaction or reactions that are being monitored. As the frequency of measurements gets lower, the time between measurements gets longer. One way to characterize a binding reaction is to refer to the time at which half of the analyte will be bound (t_(1/2)). The binding reactions of the disclosure can have a (t_(1/2)) from on the order of milliseconds to on the order of hours, thus the frequency of measurements can vary by a wide range. The time between measurements will generally not be even over the time of the binding reaction. In some embodiments, a short time between of measurements will be made at the onset of the reaction, and the time between measurements will be longer toward the end of the reaction. One advantage of the present disclosure is the ability to measure a wide range of binding rates. A high initial frequency of measurements allows the characterization of fast binding reactions which may have higher binding, and lower frequency of measurements allows the characterization of slower binding reactions. For example, points can initially be measured at a time between points on the order of a microsecond, then after about a millisecond, points can be measured at a time between points on the order of a millisecond, then after about a second, time points can be measured at a time between points on the order of a second. Any function can be used to ramp the change in measurement frequency with time. In some cases, changes in the reaction conditions, such as stringency or temperature changes will be made during a reaction, after which it may be desirable to change the frequency of measurements to measure the rates of reaction which will be changed by the change in reaction condition.

In some embodiments, a probe may have substantially no analyte bound to it at the beginning of the binding reaction, then the probe may be exposed to a solution containing the analyte, and the analyte may begin to bind, with more analyte bound to the probe with time. In some cases, the reaction will reach saturation, the point at which all of the analyte that is going to bind has bound. Generally, saturation will occur when a reaction has reached steady state. At steady state, in a given time period, just as many analytes are released as new analytes are bound (the on rate and off rate are equal). In some cases, with very strong binding, where the off-rate for the analyte is essentially zero, saturation will occur when substantially all of the analyte that can bind to the probe will have bound, has bound. Thus, while it may be advantageous to measure a change in signal with time that can be correlated with binding kinetics, the measurement of a signal that does not change with time also provides information in the context of a real-time experiment, and can also be useful in the present disclosure. For example, in some cases the absence of a change in the signal will indicate the level of saturation. In other cases the absence of a change in signal can indicate that the rate of the reaction is very slow with respect to the change in time measured. It is thus a beneficial aspect of this disclosure to measure binding event in real time both where signals change with time and where the signals do not change with time.

One aspect of the methods of the present disclosure provides the measurement of concentration of an analyte from the measurement of binding kinetics. Since analyte binding rate can be concentration-dependent, we can estimate the analyte abundance in the sample solution using binding rates.

One aspect of the present disclosure provides the determination of the binding of analyte to probe by measuring the rate near the beginning of the reaction. In addition to providing a more reliable estimate of C, measurement near the beginning of the reaction can shorten the time that is required to measure analyte binding over the time required for measuring binding from saturation. In some embodiments of the disclosure, the binding is measured during the time for less than about the first 0.1, 0.5, 1, 2, 3, 4, 5, 6, 8, 10, 12, 14, 18, 20, 25, 30, 40, 50, 60, 70, 80, or 90 percent of the analyte to bind as compared to the amount of analyte bound at saturation. In some embodiments, the binding kinetics are determined in a time for less than about the first 20% of the analyte to bind. In some embodiments, the binding kinetics are determined in a time for less than about the first 1-2% of the analyte to bind.

I. Molecular Recognition Layer

A molecular recognition layer of the present disclosure may comprise an open surface of the biosensor array.

A molecular recognition layer of the present disclosure may comprise a plurality of probes located at independently addressable locations for detecting different analytes. The probes can specifically bind with analytes in solution in order to determine the concentration and binding characteristics of the analytes. The probes can be used to detect analytes including, but not limited to, polymers, hormones, DNA strands, proteins, and bacteria. In some embodiments, the molecular recognition layer comprises 2 to 1,000,000 probes.

In some cases, the independently addressable regions comprise probes that are fluorescent moieties. The fluorescent moieties can also be bound to the probes. The probe-bound fluorescent moieties can be quenched by analytes comprising quenchers, such that the quenching of fluorescence can be used to determine the concentration of analyte in solution. The molecular recognition layer can transmit light through an optical layer to a sensor layer in a biosensor array of the disclosure. Often, the light is transmitted by fluorescence from the interaction and binding of an analyte to a probe through the optical layer to the sensor layer.

In some embodiments, the fluorescent moieties are bound to the surface of the array, and are not covalently bound to the probes. Surface bound fluorescent moieties can be quenched by analytes in solution comprising quenchers and thus used to determine the concentration of analyte in solution even where the fluorescent moiety is not bound to the probe itself.

In an embodiment, the probes of the molecular recognition layer are nucleic acids. The probes can also be proteins.

In other embodiments, the RT-μArray is placed onto a transducer array. The distance of the probes to the transducer array in such a setup can be from 1 mm to 0.1 μm. In some embodiments, the distance is about 20 μm to 2 μm.

The arrays of the present disclosure may comprise probes which may comprise a molecular recognition layer. The layer may be biological, nonbiological, organic, inorganic, or a combination of any of these. The surface on which the probes reside can exist as particles, strands, precipitates, gels, sheets, tubing, spheres, containers, capillaries, pads, slices, films, plates, slides, semiconductor integrated chips, etc. The surface is preferably flat but may take on alternative surface configurations. For example, the molecular recognition layer may occur on raised or depressed regions on which synthesis or deposition takes place. In some embodiments, the molecular recognition layer will be chosen to provide appropriate light-absorbing characteristics. For example, the layer may be a polymerized Langmuir Blodgett film, functionalized glass, Si, Ge, GaAs, GaP, SiO₂, SiN₄, modified silicon, or any one of a variety of gels or polymers such as (poly)tetrafluoroethylene, (poly)vinylidendifluoride, polystyrene, polycarbonate, or combinations thereof.

The surface can be a homogeneous solid and/or unmoving mass much larger than the capturing probe where the capturing probes are confined and/or immobilized within a certain distance of it. In certain embodiments, the surface is planar with roughness of 0.1 nm to 100 nm, e.g., between 1 nm to 10 nm. In other embodiments the surface can be a porous surface with roughness of larger than 100 nm. In other embodiments, the surface can be non-planar. Examples of non-planar surfaces are spherical magnetic beads, spherical glass beads, and solid metal and/or semiconductor and/or dielectric particles.

The molecular recognition layer may be in contact with fluid that is optically transparent to an excitation source light. After excitation of the molecular recognition layer, the layer can emit an optical wavelength that can be detected.

In some embodiments, the molecular recognition layer may be bound to a glass surface when the optical layer comprises glass. The molecular recognition layer can also be bound to silica, silicon, plastic, metal, metal-alloy, nanopore, polymeric, and nylon. The surfaces to which the molecular recognition layer is bound can be treated with a layer of chemicals prior to attaching probes to enhance the binding or to inhibit non-specific binding during use. For example, glass surfaces can be coated with self-assembled monolayer (SAM) coatings, such as coatings of as aminoalkyl silanes, or of polymeric materials, such as acrylamide and proteins.

Probes can be attached covalently (but non-covalent attachment methods can also be used). A number of different chemical surface modifiers can be added to the surface to attach the probes. Examples of chemical surface modifiers include N-hydroxy succinimide (NHS) groups, amines, aldehydes, epoxides, carboxyl groups, hydroxyl groups, hydrazides, hydrophobic groups, membranes, maleimides, biotin, streptavidin, thiol groups, nickel chelates, photoreactive groups, boron groups, thioesters, cysteines, disulfide groups, alkyl and acyl halide groups, glutathiones, maltoses, azides, phosphates, and phosphines. Glass slides with such chemically modified surfaces are commercially available for a number of modifications. These can easily be prepared for the rest, using standard methods (Microarray Biochip Technologies, Mark Schena, Editor, March 2000, Biotechniques Books).

In some embodiments, surfaces that are reactive to probes comprising amines are used. An advantage of this reaction is that it is fast, with no toxic by-products. Examples of such surfaces include NHS-esters, aldehyde, epoxide, acyl halide, and thio-ester. Most proteins, peptides, glycopeptides, etc. have free amine groups, which will react with such surfaces to link them covalently to these surfaces. Nucleic acid probes with internal or terminal amine groups can also be synthesized, and are commercially available (e.g., from IDT or Operon). Thus, nucleic acids can be bound (e.g., covalently or non-covalently) to surfaces using similar chemistries.

The surfaces to which the probes are bound need not be reactive towards amines, but can be easily converted into amine-reactive surfaces with coatings. Examples of coatings include amine coatings (which can be reacted with bis-NHS cross-linkers and other reagents), thiol coatings (which can be reacted with maleimide-NHS cross-linkers, etc.), gold coatings (which can be reacted with NHS-thiol cross linkers, etc.), streptavidin coatings (which can be reacted with bis-NHS cross-linkers, maleimide-NHS cross-linkers, biotin-NHS cross-linkers, etc.), and BSA coatings (which can be reacted with bis-NHS cross-linkers, maleimide-NHS cross-linkers, etc.). Alternatively, the probes, rather than the open surface, can be reacted with specific chemical modifiers to make them reactive to the respective surfaces.

A number of other multi-functional cross-linking agents can be used to convert the chemical reactivity of one kind of surface to another. These groups can be bifunctional, tri-functional, tetra-functional, and so on. They can also be homo-functional or hetero-functional. An example of a bi-functional cross-linker is X-Y-Z, where X and Z are two reactive groups, and Y is a connecting linker. Further, if X and Z are the same group, such as NHS-esters, the resulting cross-linker, NHS-Y-NHS, is a homo-bi-functional cross-linker and may connect an amine surface with an amine-group containing molecule. If X is NHS-ester and Z is a maleimide group, the resulting cross-linker, NHS-Y-maleimide, is a hetero-bi-functional cross-linker and may link an amine surface (or a thiol surface) with a thio-group (or amino-group) containing probe. Cross-linkers with a number of different functional groups are widely available. Examples of such functional groups include NHS-esters, thio-esters, alkyl halides, acyl halides (e.g., iodoacetamide), thiols, amines, cysteines, histidines, di-sulfides, maleimide, cis-diols, boronic acid, hydroxamic acid, azides, hydrazines, phosphines, photoreactive groups (e.g., anthraquinone, benzophenone), acrylamide (e.g., acrydite), affinity groups (e.g., biotin, streptavidin, maltose, maltose binding protein, glutathione, glutathione-S-transferase), aldehydes, ketones, carboxylic acids, phosphates, hydrophobic groups (e.g., phenyl, cholesterol), etc. Such cross-linkers can be reacted with the surface or with the probes or with both, in order to conjugate a probe to a surface.

Other alternatives include thiol reactive surfaces such as acrydite, maleimide, acyl halide and thio-ester surfaces. Such surfaces can covalently link proteins, peptides, glycopeptides, etc., via a (usually present) thiol group. Nucleic acid probes containing pendant thiol-groups can also be easily synthesized.

Alternatively, one can modify glass surfaces with molecules such as polyethylene glycol (PEG), e.g. PEGs of mixed lengths

Other surface modification alternatives (such as photo-crosslinkable surfaces and thermally cross-linkable surfaces) are known to those skilled in the art. Some technologies are commercially available, such as those from Mosiac Technologies (Waltham, Mass.), Exiqon™ (Vedbaek, Denmark), Schleicher and Schuell (Keene, N.H.), Surmodics™ (St. Paul, Minn.), Xenopore™ (Hawthorne, N.J.), Pamgene (Netherlands), Eppendorf (Germany), Prolinx (Bothell, Wash.), Spectral Genomics (Houston, Tex.), and Combimatrix™ (Bothell, Wash.).

Surfaces other than glass are also suitable binding the probes of the molecular recognition layer. For example, metallic surfaces, such as gold, silicon, copper, titanium, and aluminum, metal oxides, such as silicon oxide, titanium oxide, and iron oxide, and plastics, such as polystyrene, and polyethylene, zeolites, and other materials can also be used. In some embodiments, the layers of these materials will have to be made thin, e.g. less than about 100 nm in order to allow the transmission of light. The devices can also be prepared on LED (Light Emitting Diode) and OLED (Organic Light Emitting Diode) surfaces. An array of LEDs or OLEDs can be used at the base of a probe array. An advantage of such systems is that they provide easy optoelectronic means of result readout. In some cases, the results can be read-out using a naked eye.

Probes can be deposited onto the substrates, e.g., onto a modified surface, using either contact-mode printing methods using solid pins, quill-pins, ink-jet systems, ring-and-pin systems, etc. (see, e.g., U.S. Pat. Nos. 6,083,763 and 6,110,426) or non-contact printing methods (using piezoelectric, bubble-jet, syringe, electro-kinetic, mechanical, or acoustic methods. Devices to deposit and distribute probes onto substrate surfaces are produced by, e.g., Packard Instruments. There are many other methods known in the art. Example devices for depositing, e.g., spotting, probes onto substrates may include solid pins or quill pins (Telechem/Biorobotics).

In other embodiments, the molecular recognition layer is manufactured through the in-situ synthesis of the probes. This in-situ synthesis can be achieved using phosphoramidite chemistry and/or combinatorial chemistry. In some cases, the deprotection steps are performed by photodeprotection (such as the Maskless Array Synthesizer (MAS) technology, (NimbleGen, or the photolithographic process, by Affymetrix). In other cases, deprotection can be achieved electrochemically (such as in the Combimatrix procedure). Microarrays for the present disclosure can also be manufactured by using the inkjet technology (Agilent).

For the arrays of the present disclosure, the plurality of probes may be located in one addressable region and/or in multiple addressable regions on the open surface of the molecular recognition layer. In some embodiments the molecular recognition layer has about 2, 3, 4, 5, 6, or 7-10, 10-50, 50-100, 100-500, 500-1,000, 1,000-5,000, 5,000-10,000, 10,000-50,000, 50,000-100,000, 100,000-500,000, 500,000-1,000,000 or over 1,000,000 addressable regions with probes.

The spots may range in size from about 1 nm to about 10 mm, in some embodiments from about 1 to about 1000 micron and more in some embodiments from about 5 to about 100 micron. The density of the spots may also vary, where the density is generally at in some embodiments about 1 spot/cm2, in some embodiments at least about 100 spots/cm² and in other embodiments at least about 400 spots/cm², where the density may be as high as 106 spots/cm² or higher.

The shape of the spots can be square, round, oval or any other arbitrary shape.

In some embodiments it is also useful to have addressable regions which do not contain probe, for example, to act as control spots in order to increase the quality of the measurement, for example, by using binding to the spot to estimate and correct for non-specific binding.

II. Sensor Layer

The sensor layer may comprise an array of optical sensors. The sensor array may detect the light that is transmitted at the molecular recognition layer. The light that reaches the sensor array may have passed through the optical layer which comprises an optical filter layer that only allows a portion of the spectrum of light and/or certain wavelengths to reach the sensors.

The array of optical sensors can be utilized to detect analyte interaction and binding on the molecular recognition layer by receiving information from an emitted fluorescent signal. An optical sensor of the sensor layer can be positioned to correspond with each independently addressable location of the molecular recognition layer. In an embodiment, at least one or more optical sensors of the sensor layer correspond to a probe or set of probes. In an embodiment, 1 optical sensor corresponds to one independently addressable location. In another embodiment, 10-1000 optical sensors correspond to one independently addressable location. In a further embodiment, different optical sensors corresponding to the one independently addressable location measure different wavelengths of light.

In an embodiment of the disclosure, the array of optical sensors of the sensor layer is a part of a semiconductor based sensor array. The semiconductor based sensor array can be either an organic semiconductor or an inorganic semiconductor. In some embodiments, the semiconductor device is a silicon-based sensor. Examples of sensors useful in the present disclosure include, but are not limited to, a charge-coupled device (CCD), a CMOS device, and a digital signal processor. The semiconductor device of the sensor layer can also comprise an integrated in-pixel photocurrent detector. The detector may comprise a capacitive transimpedance amplifier (CTIA).

In another embodiment, the semiconductor device has an in-pixel analog to digital converter.

In another embodiment, the array of optical sensors of the sensor layer can be a photodiode array.

The sensor layer can be created using a CMOS process. A semiconductor detection platform can be the assembly of an integrated system capable of measuring the binding events of real-time microarrays (RT-μArrays). In some embodiments, an integrated device system involves a transducer array that is placed in contact with or proximity of the RT-μArray assay.

A semiconductor detection platform for RT-μArrays can include an array of independent transducers to receive and/or analyze the signal from target and probe binding events of a RT-μArray platform. A plurality of transducers can work collectively to measure a number of binding events at any individual microarray spot. For example, transducers dedicated to a spot may add and/or average their individual measured signal.

Detection circuitry connected to an array of optical sensors can be embedded in the sensor layer. Signal processing circuitry can also be connected to the array of optical sensors and embedded in the sensor layer. In some embodiments, the transducers and/or detection circuitry and/or analysis systems are implemented using electronic components which are fabricated and/or embedded in the semiconductor substrate. Examples of such fabrication techniques include, but are not limited to, silicon fabrication processes, micro-electromechanical surface micromachining, CMOS fabrication processes, CCD fabrication processes, silicon-based bipolar fabrication processes, and gallium-arsenide fabrication processes.

The transducer array can be an image sensor array. Examples of such image arrays include, but are not limited to, CMOS image sensor arrays, CMOS linear optical sensors, CCD image sensors, and CCD linear optical sensors. The image sensor can be used to detect the activity of the probe/analyte interaction within the integrated biosensor array platform.

The pixel architecture within the CMOS image sensor array can be passive pixel sensor (PPS), active pixel sensor (APS) or digital pixel sensor (DPS) as illustrated in FIG. 28. In all these architectures the light in converted to current using an integrated photodiode. The current in PPS is directly read from the photodiode by selecting the associated word and bit lines, while in APS architecture the current is initially integrated and converted to voltage and then is read. In DPS and analog-to-digital converter digitizes the read signal making the pixel output digital as opposed to analog in PPS and APS.

As used herein, the terms detector and transducer are used interchangeably, and refer to a component that is capable of detecting a signal that can be correlated with an value of analyte/probe binding.

In some embodiments the detector array is in contact with the molecular recognition layer. In some embodiments, the detector is spaced from the molecular recognition layer. The detector can be optically coupled to the molecular recognition layer, for example, with one or more lenses or waveguides.

FIG. 29 shows an example of a CMOS embodiment of the present disclosure. A semiconductor is utilized as a sensor for detecting the binding of the molecular recognition layer, or in this example, the detection area. The detection area is located on the device in a layer separated from the sensor layer by an optical layer.

In some embodiments, the detector is optically coupled through imaging using focal plane detector arrays: In this method the signal generated from the system is focused on a focal point detector array. This approach useful for optical detection systems where signal focusing can be carried out using lenses and other optical apparatus. Examples of detectors in these embodiments are CMOS and CCD image sensors.

Detectors can be placed such that the signal generated from the capturing region can only be observed by the dedicated detector. If a microarray with multiple capturing spots is used, multiple detectors are used, each dedicated to an individual spot.

The detectors of the present disclosure are generally capable of capturing signal at multiple time points in real-time, during the binding reaction. In some embodiments the detector is capable of measuring at least two signals in less than about 1 psec, 5 psec, 0.01 nsec, 0.05 nsec, 0.1 nsec, 0.5 nsec, 1 nsec, 5 nsec, 0.01 μsec, 0.05 μsec, 0.1 μsec, 0.5 μsec, 1 μsec, 5 μsec, 0.01 msec, 0.05 msec, 0.1 msec, 0.5 msec, 1 msec, 5 msec, 10 msec, 50 msec, 100 msec, 0.5 sec, 1 sec, 5 sec, 10 sec, or 60 sec.

In some embodiments the detector detects the signal at the substrate. In some embodiments the detector will detect the signal in the solution. In some embodiments, the detector will detect signal in both the solution and at the molecular recognition layer.

Where the detector is capable of detecting optical signals, the detector can be, for example a photomultiplier tube (PMT), a CMOS sensor, or a CCD sensor. In some embodiments, the detector comprises a fiber-optic sensor.

In some embodiments, the device comprising the sensor is capable of sensitive fluorescent measurements including synchronous fluorimetry, polarized fluorescent measurements, laser induced fluorescence, fluorescence decay, and time resolved fluorescence.

III. Optical Layer

The biosensor arrays of the present disclosure may comprise an optical layer. The fully integrated arrays of the present disclosure may comprise an optical layer that at least comprises an optical filter layer. The optical layer resides between the molecular recognition layer and the sensor layer, and transmits the light from the molecular recognition layer to the sensor layer.

An optical layer of the biosensor array can comprises an optical filter layer for transmitting a portion of the spectrum of light from the molecular recognition layer to the sensor layer. The optical filter layer can be a band-pass, stop-band, and/or low-pass optical filter. In a non-limiting example, the optical filter has a bandwidth of about 10 nm to about 20 nm. In this context, the term bandwidth refers to the range of wavelengths that is either passed by a band pass filter, or the range of wavelengths that are stopped by a stop filter. In some embodiments, the optical filter is in the wavelength range of 400 nm to 800 nm.

The choice of the wavelength characteristics of the optical filter layer depends on the characteristics of the fluorescent moieties that are used. In some embodiments, a band-pass filter is used that cuts off light corresponding to excitation, but allows transmission of light corresponding to emission of fluorescence. In some embodiments, the optical filter attenuates fluorescent excitation light by a factor of 102 to 107. In some embodiments, the optical filter attenuates fluorescent excitation light by a factor of 103 to 105.

In some embodiments, the optical filter is a multilayer dielectric filter which covers the transducers.

In some embodiments of the disclosure with optical layers, the photon flux from the molecular recognition layer is guided to the transducer array, using a plurality of optical waveguides that are of the optical coupling layer. The optical waveguides can operate to essentially map the emitted photon flux from the molecular recognition layer onto the transducer array. The optical coupling layer can comprise a plurality of optical waveguides. Examples of signal coupling elements include fiber optic cables, fiber optic bundles, fiber optic faceplates, and light pipes. Thus, pluralities of transducers and/or spots are optically connected to each other. In further embodiments of this disclosure, the waveguide is a phaseplate system.

The optical layer can integrate the biochemical part of the microarray with an emission filter and a photo-detector in CMOS where the molecular recognition layer is immobilized on a planar surface of an optical layer. The excitation photon flux tends to be orthogonal to the surface of the microarray, but the emission is in all directions. In order to capture most of the emitted photons, an optical coupling layer comprising a fiber-optic faceplate (FOF) comprising densely packed optical fibers can be positioned on top of the optical filter. The FOF prohibits light scattering and can guide a 2D fluorescence optical pattern along the direction of its fibers. The FOF can be 2 μm to 20 cm thick. In some embodiments, the thickness of the FOF is in the range of about 5 μm to 1 cm. In an embodiment, the thickness of the FOF is 3 mm. The FOF thermally isolates the microarray assay from the CMOS die and photodiodes as well as creating a distance between the aqueous solution and the chip.

An example device of the disclosure comprising an FOF is illustrated in FIG. 30. The FOF is located below a capturing (or molecular recognition layer). When the fluorophores are bound to the capture layer, the emitted photon flux can travel through the fiber optics of the FOF in order to send a greater amount of emitted photons to the sensor layer without allowing the excitation photon flux (Fx) through to the sensor layer. In this example, the FOF is 3 mm thick and the optical filter layer is 2.1 μm thick. The optical layer can transmit the photon flux from capture layer that has traveled through the FOF to a CMOS image sensor layer. In this example, the CMOS sensor is about 1 mm thick and comprises structures (“metal curtains”) for directing the photon flux to a photodiode sensor embedded in the CMOS sensor layer. There are two photodiodes corresponding to the two independently addressable locations on the molecular recognition layer of the example embodiment. Readout circuitry for transmitting the information captured by the photodiodes is also embedded in the CMOS sensor layer.

As an example, the sensor array shown in FIG. 30 can be fabricated using a standard digital 0.35 μm CMOS process in an area of 9 mm². The filter is fabricated using layer-by-layer deposition of dielectric materials to create a long-pass filter with transition wavelength of 560 nm on the FOF. The FOF is the cut to match the sensor array area and placed on top of the CMOS chip. To physically stabilize the FOF on the chip, a non-conductive epoxy is applied on the periphery. The surface functionalization to immobilize the probe is then carried out on the surface of the FOF. In some embodiments, the surface of the FOF can be SiO₂ and very similar to the surface of glass slides.

In an aspect of the present disclosure, a biosensor system is disclosed that comprises an embodiment of a biosensor array of the disclosure, a light source that directs light to the biosensor array, a fluidic chamber for holding fluid in contact with the biosensor array, a temperature controller for controlling the temperature of the fluid and/or the molecular recognition layer, and an interface that connects to the biosensor array to allow electronic communication to and from the array.

The system may comprise a light source, for example, for excitation of fluorescence. The light source is generally optically coupled to the substrate, for example with one or more lenses or waveguides. The light source can provide a single wavelength, e.g., a laser, or a band of wavelengths.

The light source that directs light to the biosensor array the light source can be fixed and illuminate some or all of the addressable locations on a molecular recognition layer of the biosensor array.

In an embodiment, the system comprises a plurality of biosensor arrays, wherein at least two of the biosensor arrays are connected to the same computer. In a further embodiment, the system can comprise 2 to 12 biosensor arrays, all of which are connected to the same computer. This system allows for the measurement of binding on multiple arrays simultaneously in one instrument using one computer system.

Control of temperature can be important to allow control of binding reaction rates, e.g. by controlling stringency. The temperature can be controlled by controlling the temperature at any place within the system including controlling the temperature of the fluid or the temperature of the molecular recognition layer. Any temperature control can be used for controlling the temperature including, but not limited to, resistive heaters, Peltier devices, infrared heaters, fluid flow, and gas flow. The temperatures can be the same or different for solution or substrate or different parts of each. In a preferable embodiment, the temperature is consistent within the binding region. In some embodiments, the temperature is controlled to within about 0.01, 0.05, 0.1, 0.5, or 1° C.

In some embodiments, the temperature can be rapidly changed during the binding reaction. The system can be capable of changing the temperature at a rate of temperature change corresponding to a change of 1° C. in less than about 0.01 msec, 0.1 msec, 0.5 msec, 1 msec, 5 msec, 10 msec, 50 msec, 100 msec, 0.5 sec, 1 sec, 10 sec, or 60 sec.

In other embodiments, the temperature is changed slowly, gradually ramping the temperature over the course of the binding reaction.

An example of changing the temperature during the binding reaction involves a change in temperature to change the binding stringency and probability. Many bindings in affinity-based biosensors are a strong function of temperature, thus by changing temperature, the stringency can be altered, and the new capturing process can be observed with a new set of capturing probabilities.

The system can further be capable of measuring temperature at one or multiple locations in the solution or on the biosensor array. The temperature can be measured by any means including, but not limited to, by thermometer, thermocouple, or thermochromic shift.

When temperature is measured, the system can utilize a feedback loop for temperature control wherein the measured temperature is used as an input to the system in order to more accurately control temperature.

A control system of a system of the disclosure can be a real-time control system for reading the real-time measurements from a biosensor array of the disclosure.

FIG. 31 shows a block diagram of some of the components of systems of the present disclosure. The example system may comprise (i) a biosensor array which includes a molecular recognition layer comprising probes and analytes, (ii) a light source for illuminating the molecular recognition layer of the biosensor array, (iii) heating and cooling modules and a temperature sensor, (iv) a temperature controller, and (v) a computer to which sensor data is sent from the biosensor array. In some embodiments, the sensor data will be raw output from the optical sensors. In other embodiments, the sensor data sent to the computer may be further processed by circuits within the optical sensor array.

The system can comprise a computing system for analyzing detected signals. In some embodiments, the system is capable of transferring time point data sets to the computing system wherein each time point data set corresponds to detected signal at a time point, and the computing system is capable of analyzing the time point data sets, in order to determine a property related to the analyte and probe. Thus, a computer system and software that can store and manipulate the data (for instance, images taken at time points) may be components of the system. The data can be analyzed in real-time, as the reaction unfolds, or may be stored for later access.

The information corresponding to a detected signal at each time point can be single values such as signal amplitude, or can be more complex information, for example, where each set of signal information corresponds to an image of a region containing signal intensity values at multiple places within an addressable location.

The property related to analyte and/or probe can be, for example, analyte concentration, binding strength, or competitive binding, and cross-hybridization.

In some embodiments, the computing system uses algorithms for determining concentration and/or cross-hybridization.

The system can also comprise a computer with software for process control and data collection and analysis. The software can be used for characterizing binding between analyte and probe. In one embodiment, the software carries out at least one of the steps of i) accessing stored images taken at different time points, ii) performing image processing to determine the location of the spots and convert the data to a collection of time series (one for each spot) representing the temporal behavior of the signal intensity for each spot, and iii) for each spot on the array determining whether a reaction has happened (this is often done by comparing with control spots on the array). Optionally, the software can perform the steps of iv) determining whether the reaction at each spot involves the binding of a single analyte or multiple analytes (if, for example, cross-hybridization is occurring), v) estimating the reaction rates using statistical system identification methods. Examples of statistical system identification methods include methods such as Prony's method. In the case that step iv) is used, (multiple bindings per spot), the reaction rate of each binding is determined, and vi) using the reaction rates to estimate the unknown quantity of interest (analyte concentration, binding strength, etc.) using, for example optimal Bayesian methods.

In some embodiments, the system will have software for interfacing with the instrument, for example, allowing the user to display information in real-time and allowing for user to interact with the reaction (i.e., add reagents, change the temperature, change the pH, dilution, etc.).

The system can comprise control circuitry that enables users to activate readout circuits and sensors on the array. The control circuitry can also be used to specify temperature, mixing, fluorescent wavelength, fluorescent excitation power, pressure, and/or humidity. In addition, the control circuitry can be a part of the biosensor array.

In another embodiment, the biosensor system comprises decoder circuitry to select which of a plurality of sensors are to be used. At least part of the decoder circuitry can be part of the biosensor array. The decoder can select which of the plurality of transducers are to be used to analyze the biosensor array probe. The control circuitry enables a user to activate a combination of read-out circuitries and transducers. Further, the system includes a function generator coupled to the control circuitry to generate the experiment control signals. The control signals are connected to systems inside and/or outside the semiconductor substrate. In certain embodiments, the control signal specifies the measurement parameters. These parameters include, but are not limited to, the biosensor array assay temperature, mixing speed, fluorescent excitation signal wavelength, fluorescent excitation power, pressure, and humidity. In further embodiments the control signals are generated by processing the measured signals. The processing can be carried out using a digital signal processor outside the semiconductor substrate and/or an embedded digital signal processing unit inside the semiconductor substrate.

In an embodiment of the disclosure illustrated in FIG. 32, a system can comprise an assay kit, a disposable sensor chip, a computer chip reader and software for executing a method of the disclosure. The assay kit can comprise the necessary reagents for sample preparation and labeling of RT-μArray experiments. The sensor chip can comprise a CMOS chip with spotted capturing probes for measuring the level of hybridization in real-time. The chip reader can be a dedicated reader for the disposable sensor chip and may or may not comprise a temperature controller, excitation signal generator, and data acquisition means.

The integrated biosensor array devices and systems of the disclosure can evaluate the abundance of a plurality of target analytes in the sample by real-time detection of target-probe binding events. In certain embodiments, the integrated biosensor arrays are used as RT-μArray detection systems to measure the concentration of the target analytes by analyzing the binding rates and/or the equilibrium concentration and/or the fluctuation of the captured analytes in a single and/or plurality of spots. Applications of integrated biosensor array devices and systems are within the field of Genomics and Proteomics, in particular DNA and Protein microarrays and immunoassays. In some embodiments, the disclosed devices, systems, and methods do not require any washing step and can also measure the probe density variations prior to hybridization (thus allowing for pre-calibration of the experimental results). The RT-μArray systems can also carry out various time averaging schemes to suppress the Poisson noise and fluctuation of target bindings. Since target concentrations can be determined by the reaction rates, it is not necessary for the hybridization process to go to equilibrium, resulting in faster detection times. A goal of the disclosure is to increase the dynamic range, sensitivity and resolution of microarrays. The disclosure allows for quality control and may be more amenable to integration and to automation.

Advantages offered by the present disclosure can also apply to RNA, protein, carbohydrate, or lipid microarrays, to analyze interactions among molecules of the same or of different biochemical nature. In particular, real-time measurements by a platform of the disclosure, in which interactions are detected as they occur, allows for measuring and comparing rates of analyte binding, affinities, etc. In addition, the RT-μArray can consist of microarrays in which compounds of two different biochemical classes (for example, protein and DNA, or carbohydrate and DNA) are positioned together as a mixture on the same spot of the microarray.

Uses

The methods and systems of the present disclosure can be used to measure nucleotide sequences in a variety of sample types including cDNA, genomic DNA, RNA, cells, or viruses.

The methods and systems of the present disclosure may be used for determining the presence and/or amount of multiple nucleotide sequences in a sample. Where the probe and analyte are nucleic acids, the present disclosure provides methods of expression monitoring and or measuring genetic information. The methods and systems of the present disclosure may allow for a plurality of nucleotide sequences relating to genes, e.g. 10, 100, 1,000, 10,000, 100,000, or more genes to be analyzed at once. The term expression monitoring is used to refer to the determination of levels of expression of particular, typically preselected, genes. For example, amplicons derived from nucleic acid samples such as messenger RNA that reflect the amount of expression of genes are hybridized to the arrays during or after amplification cycles, and the resulting hybridization signal as a function of time provides an indication of the amount of amplicon which can then be used to determine the level of expression of each gene of interest. In some cases, the whole transcriptome can be measured comprising all or a substantial portion of the expression in a cell, or group of cells. In some embodiments the expression of only a few genes, such as 5 to 100 genes is measured, for example, to diagnose a specific condition. In some embodiments, the array has a high degree of probe redundancy (multiple probes per gene) the expression monitoring methods provide accurate measurement and do not require comparison to a reference nucleic acid.

In another embodiment, this disclosure provides generic difference screening methods that identify differences in the abundance (concentration) of particular nucleic acids in two or more nucleic acid samples. The generic difference screening methods involve hybridizing two or more nucleic acid samples to the same oligonucleotide array, or to different oligonucleotide arrays having the same oligonucleotide probe composition, and optionally the same oligonucleotide spatial distribution. The resulting hybridizations are then compared allowing determination which nucleic acids differ in abundance (concentration) between the two or more samples.

Where the concentrations of the nucleic acids comprising the samples reflects transcription levels genes in a sample from which the nucleic acids are derived, the generic difference screening methods permit identification of differences in transcription (and by implication in expression) of the nucleic acids comprising the two or more samples. The differentially (e.g., over- or under) expressed nucleic acids thus identified can be used (e.g., as probes) to determine and/or isolate those genes whose expression levels differs between the two or more samples.

The methods and systems of the present disclosure may be used in a wide variety of circumstances including detection of disease, identification of differential gene expression between two samples (e.g., a pathological as compared to a healthy sample), screening for compositions that upregulate or downregulate the expression of particular genes, and so forth. They can be used for the analysis of genetic DNA including determination of single-nucleotide polymorphisms (SNPs) for genotyping and allele discrimination assays and for the detection of DNA and RNA viruses. The methods and systems of the invention can also be used for the detection of genetically modified organisms (GMO).

The methods and systems of the present disclosure can be used for genetic testing and diagnostics. They can be used for example for newborn screening (e.g. for phenylketonuria or congenital hypothyroidism; diagnostic testing (such as to diagnose or rule out a specific genetic or chromosomal condition or to confirm a diagnosis when a particular condition is suspected based on physical mutations and symptoms); carrier testing: (e.g. to identify people who carry one copy of a gene mutation that, when present in two copies, predictive and presymptomatic testing: (for example, testing for BRCA1 in relation to the risk of breast cancer); forensic testing (e.g. to identify an individual for legal purposes, e.g. to identify crime or catastrophe victims, rule out or implicate a crime suspect, or establish biological relationships between people (for example, paternity); or for research testing (e.g. finding unknown genes, learning how genes work and advancing our understanding of genetic conditions).

EXAMPLES Example 1

This example demonstrates the use of a sample real-time microarray to measure the binding of multiple analytes to multiple probes.

FIG. 10 shows the layout of a 6×6 DNA microarray. Three different DNA probes (1, 2, and Control) with three different concentrations (2 μM, 10 μM, and 20 μM) are spotted and immobilized on the surface as illustrated. The probes contain a single Cy3 fluorescent molecule at the 5′ end. The DNA targets in this experiment contain a quencher molecule. The analyte binding in this system results in quenching of fluorescent molecules in certain spots. FIG. 11 shows a few samples of the real-time measurements of the microarray experiment wherein the control targets are added to the system. As illustrated in FIG. 11, the spots are quenched due to analyte binding.

FIGS. 12-15 each show data for 4 different spots with similar oligonucleotide capturing probes. The target DNA analyte is introduced in the system at time zero and quenching (reduction of signal) occurs only when binding happens. For FIG. 12, the light intensity coefficient of variation was about 15%, however the estimated time constant rate from real-time measurements had only 4.4% variations. For FIG. 13 the light intensity coefficient of variation was about 15%, however the estimated time constant rate from real-time measurements had only 2.1% variations. For FIG. 14 the light intensity coefficient of variation was about 22%, however the estimated time constant rate from real-time measurements had only 6% variations. For FIG. 15 the light intensity coefficient of variation was about 22%, however the estimated time constant rate from real-time measurements had only a 4.8% variation.

In FIG. 16, the signals measured during two real-time experiments wherein target 2 is applied to the microarray, first at 2 ng and then at 0.2 ng, are shown. The measured light intensities at the corresponding probe spots decay over time as the targets to the probes bind and the quenchers come in close proximity to the fluorescent labels attached to the end of the probes. The rate of the decay, which can be estimated by a curve fitting technique, is proportional to the amount of the target present. The time constant of the measured process is defined as the inverse of the rate of decay. The ratio of the time constants of the two processes is 10, which is precisely the ratio of the amounts of targets applied in the two experiments.

Example 2

This example provides a derivation of an algorithm, and the use of the algorithm to determine analyte concentration such as amplicon concentration, from a real-time binding data. The derivation proceeds as follows:

Assume that the hybridization process starts at t=0, and consider discrete time intervals of the length Δt. Consider the change in the number of bound target molecules during the time interval (iΔt, (i+1)Δt). We can write

n _(b)(i+1)−n _(b)(i)=[n _(t) −n _(b)(i)]p _(b)(i)Δt−n _(b)(i)p _(r)(i)Δt,

-   -   where n_(t) denotes the total number of target molecules,         n_(b)(i) and n_(b)(i+1) are the numbers of bound target         molecules at t=iΔt and t=(i+1)Δt, respectively, and where         p_(b)(i) and p_(r)(i) denote the probabilities of a target         molecule binding to and releasing from a capturing probe during         the i^(th) time interval, respectively. Hence,

$\begin{matrix} {\frac{{n_{b}\left( {i + 1} \right)} - {n_{b}(i)}}{\Delta \; t} = {{\left\lbrack {n_{t} - {n_{b}(i)}} \right\rbrack {p_{b}(i)}} - {{n_{b}(i)}{{p_{r}(i)}.}}}} & (1) \end{matrix}$

It is reasonable to assume that the probability of the target release does not change between time intervals, i.e., p_(r)(i)=p_(r), for all i. On the other hand, the probability of forming a target-probe pair depends on the availability of the probes on the surface of the array. If we denote the number of probes in a spot by n_(p), then we can model this probability as

$\begin{matrix} {{{p_{b}(i)} = {{\left( {1 - \frac{n_{b}(i)}{n_{p}}} \right) - p_{b}} = {\frac{n_{p} - {n_{b}(i)}}{n_{p}}p_{b}}}},} & (2) \end{matrix}$

-   -   where p_(b) denotes the probability of forming a target-probe         pair assuming an unlimited abundance of probes.

By combining (1) and (2) and letting Δt→0, we arrive to

$\begin{matrix} {\frac{{dn}_{b}}{dt} = {{{\left( {n_{t} - n_{b}} \right)\frac{n_{p} - n_{b}}{n_{p}}p_{p}} - {n_{b}p_{r}}} = {{n_{t}p_{b}} - {\left\lbrack {{\left( {1 + \frac{n_{t}}{n_{p}}} \right)p_{b}} + p_{r}} \right\rbrack n_{b}} + {\frac{p_{b}}{n_{p}}n_{b}^{2}}}}} & (3) \end{matrix}$

Note that in (3), only nb=nb(t), while all other quantities are constant parameters, albeit unknown. Before

-   -   proceeding any further, we will find it useful to denote

$\begin{matrix} {{\alpha = {{\left( {1 + \frac{n_{t}}{n_{p}}} \right)p_{b}} + p_{r}}},{\beta = {n_{t}p_{b}}},{\gamma = {\frac{p_{b}}{n_{p}}.}}} & (4) \end{matrix}$

Clearly, from (4),

${p_{b} = \frac{\beta}{n_{t}}},{n_{p} = \frac{p_{b}}{\gamma}},{p_{r} = {\alpha - {\left( {1 + \frac{n_{t}}{n_{p}}} \right){p_{b}.}}}}$

Using (4), we can write (3) as

$\begin{matrix} {{\frac{{dn}_{b}}{dt} = {{\beta - {\alpha \; n_{b}} + {\gamma \; n_{b}^{2}}} = {{\gamma \left( {n_{b} - \lambda_{1}} \right)}\left( {n_{b} - \lambda_{2}} \right)}}},} & (5) \end{matrix}$

-   -   where λ₁ and λ₂ are introduced for convenience and denote the         roots of

β−αn _(b) +γn _(b) ²=0.

Note that γ=β/(λ₁λ₂). The solution to (5) is found as

${n_{b}(t)} = {\lambda_{1} + {\frac{\lambda_{1}\left( {\lambda_{1} - \lambda_{2}} \right)}{{\lambda_{2}e^{{\beta {({\frac{1}{\lambda_{1}} - \frac{1}{\lambda_{2}}})}}t}} - \lambda_{1}}.}}$

We should point out that (3) describes the change in the amount of target molecules, nb, captured by the probes in a single probe spot of the microarray. Similar equations, possibly with different values of the parameters np, nt, pb, and pr, hold for other spots and other targets.

Estimating Parameters of the Model

The following is an outline of a procedure for estimation of the parameters. Ultimately, by observing the hybridization process, nt, np, pb, and pr may be obtained. However, we do not always have direct access to nb(t) in (6), but rather to yb(t)=knb(t), where k denotes a transduction coefficient. In particular, we observe

$\begin{matrix} {{{y_{b}(t)} = {\lambda_{1}^{*} + \frac{\lambda_{1}^{*}\left( {\lambda_{1}^{*} - \lambda_{2}^{*}} \right)}{{\lambda_{2}^{*}e^{{\beta {({\frac{1}{\lambda_{1}^{*}} - \frac{1}{\lambda_{2}^{*}}})}}t}} - \lambda_{1}^{*}}}},} & (7) \end{matrix}$

-   -   where λ₁*=kλ₁, λ₂*=kλ₂, and β*=kβ.

For convenience, we also introduce

$\begin{matrix} {{\gamma^{*} = {\frac{\beta}{\lambda_{1}^{*}\lambda_{2}^{*}} = \frac{\gamma}{k}}},{\alpha^{*} = {{\gamma^{*}\left( {\lambda_{1}^{*} + \lambda_{2}^{*}} \right)} = {\alpha.}}}} & (8) \end{matrix}$

From (5), it follows that

$\begin{matrix} {\beta^{*} = \left. \frac{{dy}_{b}}{dt} \middle| {}_{t = 0}. \right.} & (9) \end{matrix}$

Assume, without a loss of generality, that λ₁* is the smaller and λ₂* the larger of the two, i.e., λ₁*=min(λ₁, λ₂), and λ₂*=max(λ₁, λ₂). From (7), we find the steady-state of yb(t),

λ₁*=lim y _(b)(t), t→∞.   (10)

So, from (9) and (10) we can determine β* and λ₁*, two out of the three parameters in (7). To find the remaining one, λ₂*, one needs to fit the curve (7) to the experimental data.

Having determined β*, λ₁*, and λ₂*, we use (8) to obtain α* and γ*. Then, we should use (4) to obtain pb, pr, np, and nt from α*, β*, and γ*. However, (4) gives us only 3 equations while there are 4 unknowns that need to be determined. Therefore, we need at least 2 different experiments to find all of the desired parameters. Assume that the arrays and the conditions in the two experiments are the same except for the target amounts applied. Denote the target amounts by nt₁ and nt₂; on the other hand, pb and pr remain the same in the two experiments. Let the first experiment yield α₁*, β₁*, and γ₁*, and the second one yield α₂*, β₂*, and γ₂* (we note that γ₁*=γ₂*). Then it can be shown that

$\begin{matrix} {{p_{b} = \frac{{\beta_{1}^{*}\gamma_{1}^{*}} - {\beta_{2}^{*}\gamma_{2}^{*}}}{\alpha_{1}^{*} - a_{2}^{*}}},{and}} & (11) \\ {p_{r} = {\alpha_{1}^{*} - p_{b} - {\frac{\beta_{1}^{*}\gamma_{1}^{*}}{p_{b}}.}}} & (12) \end{matrix}$

Moreover,

$\begin{matrix} {{n_{p} = \frac{p_{b}}{k\; \gamma_{1}^{*}}},{and}} & (13) \\ {{n_{t_{1}} = {\frac{\beta_{1}^{*}\gamma_{1}^{*}}{p_{b}^{2}}n_{p}}},{n_{t_{2}} = {\frac{\beta_{2}^{*}\gamma_{2}^{*}}{p_{b}^{2}}{n_{p}.}}}} & (14) \end{matrix}$

We note that quantities (13)-(14) are known within the transduction coefficient k, where k=yb(0)/np. To find k and thus unambiguously quantify np, nt1, and nt2, we need to perform a calibration experiment (i.e., an experiment with a known amount of targets nt).

Experiments are designed to test the validity of the proposed model and demonstrate the parameter estimation procedure. To this end, two DNA microarray experiments are performed. The custom 8-by-9 arrays contain 25 mer probes printed in 3 different probe densities. The targets are Ambion mRNA Spikes, applied to the arrays with different concentrations. The concentrations used in the two experiments are 80 ng/50 μl and 16 ng/50 μl. The signal measured in the first experiment, where 80ng of the target is applied to the array, is shown in FIG. 17. The smooth line shown in the same figure represents the fit obtained according to (7). In the second experiment, 16 ng of the target is applied to the array. The measured signal, and the corresponding fit obtained according to (7), are both shown in FIG. 18.

Applying (11)-(14), we obtain

p _(b)=1.9×10³ , p _(r)=2.99×10⁵.

Furthermore, we find that

n _(t1) /n _(t2)=β₁*/β₂*=3.75.   (15)

Note that the above ratio is relatively close to its true value, 80/16=5. Finally, assuming that one of the experiments is used for calibration, we find that the value of the transduction coefficient is k=4.1×10⁻⁴, and that the number of probe molecules in the observed probe spots is np=1.6×10⁻¹¹.

Example 3

This example shows how the methods and systems of the present disclosure can be used for measurement of gene expression. Real-time microarray technology can measure, for example, expression level differences for different cell types or tissues, distinct developmental stages, cancerous versus normal cells or tissues, treated versus untreated cells or tissues, mutant versus wild-type cells, tissues or organisms.

The gene expression profiles of inflorescences of the Arabidopsis thaliana floral homeotic mutants apetala1, apetala2, apetala3, pistillata, and agamous can be compared with that of wild-type plants. By combining the data sets from the individual mutant/wild type comparisons, it is possible to identify a large number of genes that are, within flowers, predicted to be specifically or at least predominantly expressed in one type of floral organ. For each sample, floral buds from approximately 50 plants are collected, and RNA is isolated from 100 mg of tissue with the RNeasy RNA Isolation Kit (Qiagen). To prepare labeled target material from those samples, an in vitro transcription amplification method followed by aminoallyl-UTP-mediated labeling is used. In brief, first and second strand cDNA is synthesized from 3 μg of total RNA using a polyA-primer with a T7 promoter sequence. Then in vitro transcription is performed using the Megascript T7 kit (Ambion), in the presence of aminoallyl-UTP and of a reduced amount of UTP, to incorporate the modified aaUTP into the aRNA during the transcription process. Finally, dye molecules (Cy3 Mono-Reactive Dye, Cy5 Mono-Reactive Dye, Amersham) are coupled to the amplified RNA and the dye-labeled RNA is fragmented before hybridization. These and similar protocols are well established in the microarray field and are well known to those skilled in the art, and commercial kits are available for cDNA synthesis, in vitro transcription amplification, and amino-allyl labeling, such as the Amino Allyl MessageAmp™ II aRNA Amplification Kit, from Ambion. Aminoallyl UTP contains a reactive primary amino group on the C5 position of uracil that can be chemically coupled to N-hydroxysuccinimidyl ester-derivatized reactive dyes (NHS ester dyes), in a simple efficient reaction.

Amine-reactive quenchers are commercially available, for example QSY® 9 carboxylic acid, succinimidyl ester, from Invitrogen. The real-time microarray technology is used with minimal modifications to the sample preparation and labeling procedures: namely, with the simple substitution of the QSY-9 ester for the Cy-dye ester. In this case, total RNA samples are prepared as described above. The purified total RNA is then amplified using the Amino Allyl MessageAmp™ II aRNA Amplification Kit, from Ambion, and the resulting aRNA is labeled with QSY9. This labeled RNA population is then used in hybridization with Arabidopsis real-time microarrays. Such arrays consist of an arranged collection of probes that correspond to all (or a subset of) the genes in the Arabidopsis genome. The oligonucleotide probes are labeled with a fluorescent moiety (such as Cy3) and printed by contact deposition onto CodeLink slides (GE Healthcare), which are processed and blocked after printing following manufacturer's instructions.

Example 4

This example relates to using an algorithm to measure cross-hybridization. A variety of different techniques to recover the signal, including, but not limited to, total least squares, ESPRIT, and Prony's method, (see Dowling et. al. IEEE Trans. on Antennas and Propag., vol. 42, no. 5, 1994 and van der Veen et al. Proc. of the IEEE, 81(9):1277-1308, 1993).

In this example we study the performance of one such algorithm in simulation and illustrate the results in FIG. 19. In particular, we consider the so-called total least squares (TLS) algorithm in the situation where two target analytes bind to the same probe spot—one due to hybridization, and the other due to cross-hybridization. Parameters of the system (probabilities of hybridization, cross-hybridization, release, etc.) are chosen so as to mimic realistic experimental scenarios. The probability of hybridization is assumed to be 5 times greater than the probability of cross-hybridization (i.e., p_(h)/p_(c)=5). The number of hybridizing target is $n_(h)=10⁹$, while the number of cross-hybridizing molecules is varied. In FIG. 19, we plot the relative mean-square error of estimating n_(h) (averaged over many realizations of noise) as a function of the ratio n_(h)/n_(c). The simulation results indicate potentially successful suppression of cross-hybridization over 3 orders of magnitude of n_(h)/n_(c).

Example 5

This example illustrates how an optical filter layer in the form of a band-pass filter on the surface of the CMOS chip enhances optical performance of the integrated biosensor array. A challenge of designing any fluorescent-based detector is the proper optical excitation and detection of fluorescent labels. FIG. 33 illustrates the absorption and emission spectra of Cy3 molecule which is an example fluorophore of a system. The absorbed photon density for Cy3, denoted by, exposed to the incident photon flux, obeys the Beer-Lambert law. For a thin layer of diluted absorbing media with Cy3 as in microarray applications we have

A=F _(X)[1−e ^(−a) ⁰ ^((λ)N)]≈F _(X) a ₀(λ)N   (16)

where a₀(λ) and N are the extinction coefficient in wavelength λ and surface concentration of Cy3 respectively. Considering Q_(Y), the fluorescence quantum yield of Cy3, we can calculate I_(E), the total emitted photons per surface area by

I _(E) =Q _(Y) A≈Q _(Y) F _(X) a ₀(λ)N   (17)

As evident in FIG. 33, the photon emission is, to first order, proportional to N which is parameter of interest in microarrays. The major impediment for measuring I_(E) and therefore N, is the presence of F^(X) during detection. Although F^(X) has a different wavelength from I_(E), it is very typical for F_(X) to be to 4-5 orders of magnitude larger than I_(E) in microarray applications. To block F_(X) in our system, a multi-layer dielectric Fabry-Perot optical band-pass filter has been fabricated on the surface of a CMOS chip. This emission filter can block F_(X) by 100 dB in the Cy3 excitation band of 545-550 nm, while only loosing 25% of the signal in the pass-band.

Example 6

This example describes the construction of a fully integrated biosensor array of the present disclosure. To design the CMOS photo-detector a Nwell/Psub photodiode array is used in the 0.35 μm CMOS process. Each diode is 50 μm×50 μm and the array pitch is 250 μm. This dimension is compatible with commercial microarray specifications and also minimizes the optical cross-talk between photodiodes while providing sufficient space to integrate in-pixel a photocurrent detector and an analog to digital converter (ADC).

Most of the CMOS image sensors use direction integration, where the photocurrent is directly integrated over a reverse bias photodiode capacitor. In the design, a capacitive transimpedance amplifier (CTIA) in the pixel is used as a photocurrent integrator. Comparing with a CTIA, a direct integrator suffers from the junction capacitance variation as the reverse bias voltage changes depending on the output signal level. A CTIA does not have any such problems since the photodiode bias is regulated by an operational transimpedance amplifier (OTA) used in the CTIA and it is set to VR1 as shown in FIG. 34. Photocurrent input in the system is integrated using the feedback capacitor.

In order to take full advantage of integration capability of CMOS, an ADC is also included in the pixel level. Pixel level processing relaxes the speed requirement of ADC while removing all analog signal bus lines in the array and significantly reduces the cross-talk issues. To suppress the low frequency noise of the comparator, a chopper stabilized preamplifier has been implemented with overall voltage gain of approximately 60 dB gain.

A measurement of the concentration of Cy3 fluorophores on the surface of the chip using our integrated microarray system can be performed to determine the performance compatibility of this system with fluorescent-based microarrays.

FIG. 35 shows the die photo and the I/O pin allocation of the integrated 7 by 8 pixel biosensor array. Auxiliary circuits beside the biosensor array include row and column decoder and column switches which are necessary for the functionality of the array.

While preferred embodiments of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such embodiments are provided by way of example only. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention. It is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby. 

1. A method comprising: (a) providing a biosensor comprising: (i) a solid substrate comprising an array of semiconductor-based optical sensors; (ii) a molecular recognition layer adjacent to said solid substrate and comprising a plurality of probes corresponding to a plurality of target analytes, wherein said plurality of probes comprises different probes corresponding to different target analytes from said plurality of target analytes, wherein said plurality of probes comprise fluorophores but do not include quenchers; (b) bringing a fluid containing or suspected of containing said plurality of target analytes or derivatives thereof in contact with said molecular recognition layer of said biosensor; (c) directing excitation light from a location above said molecular recognition layer to said molecular recognition layer, and using said array of semiconductor-based optical sensors to detect signals from said molecular recognition layer by measuring said signals while said fluid is in contact with said solid substrate; and (d) using said signals to determine a presence or relative amount of said plurality of target analytes.
 2. The method of claim 1, wherein (c) comprises measuring fluorescence signals at multiple time points while said fluid is in contact with said solid substrate.
 3. The method of claim 2, wherein said fluorescence signals measured at multiple time points are upon binding of said target analytes with said plurality of probes with time, and wherein (a)-(d) are performed without washing said fluid when in contact with said solid substrate.
 4. The method of claim 3, wherein a given probe of said plurality of probes is coupled to a fluorophore and a given target analyte of said plurality of target analytes is coupled to a quencher.
 5. The method of claim 1, wherein said signals are detected upon a non-competitive interaction between a given target analyte of said plurality of target analytes and a given probe of said plurality of probes.
 6. The method of claim 1, wherein a given probe of said plurality of probes is adapted to specifically bind to a given target analyte of said plurality of target analytes.
 7. The method of claim 1, further comprising: measuring said signals at multiple time points to determine a concentration of a given target analyte of said plurality of target analytes.
 8. The method of claim 1, further comprising: measuring a change in said signals with time to determine a change in an amount of at least a subset of said plurality of target analytes bound to at least a subset of said plurality of probes with time.
 9. The method of claim 1, further comprising, prior to (b): performing nucleic acid amplification reactions on a plurality of template nucleic acid molecules to yield said plurality of target analytes as amplification products of said plurality of template nucleic acid molecules; and using said signals to detect hybridization of at least a subset of said plurality of target analytes to at least a subset of said plurality of probes while said fluid is in contact with said molecular recognition layer of said biosensor, to obtain a hybridization measurement.
 10. The method of claim 9, further comprising: using said hybridization measurement to determine a concentration of each of said subset of said plurality of target analytes.
 11. The method of claim 9, further comprising: using said hybridization measurement to determine an original amount of each of at least a subset of said plurality of template nucleic acid molecules.
 12. The method of claim 1, wherein said biosensor further comprises: an optical coupling layer adjacent to said solid substrate, which optical coupling layer is disposed between said molecular recognition layer and said array of semiconductor-based optical sensors.
 13. The method of claim 12, wherein said optical coupling layer further comprises a fiber-optic faceplate comprising packed optical fibers.
 14. The method of claim 1, wherein said molecular recognition layer comprises a control region that does not contain probes, and wherein (d) further comprises correcting for non-specific binding using signals from said control region.
 15. The method of claim 1, wherein a given probe of said plurality of probes is immobilized to said molecular recognition layer at a discrete and independently addressable location of said molecular recognition layer.
 16. The method of claim 1, wherein said molecular recognition layer comprises a plurality of discrete and independently addressable locations, wherein a given discrete and independently addressable location of said plurality of discrete and independently addressable locations comprises a given probe of said plurality of probes, wherein said given discrete and independently addressable location receives an excitation photon flux from a source in optical communication with said molecular recognition layer.
 17. The method of claim 1, wherein said plurality of target analytes and said plurality of probes are nucleic acid molecules.
 18. The method of claim 17, wherein said plurality of probes are nucleic acid molecules comprising different nucleic acid sequences.
 19. The method of claim 1, wherein a given probe of said plurality of probes comprises an energy donor.
 20. The method of claim 1, wherein a given target analyte of said plurality of target analytes comprises a quencher. 21.-23. (canceled) 